Prosthetic valve with angularly offset frames

ABSTRACT

Prosthetic valves and methods of use of prosthetic valves may be provided. In one implementation, a prosthetic valve may include an annular outer frame formed of struts intersecting at outer frame junctions, an inner frame situated within the outer frame and formed of struts intersecting at inner frame junctions, and a plurality of tissue anchors extending from the outer frame. The junctions along a downstream end of the outer frame may be spaced apart circumferentially from the junctions along a downstream end of the inner frame. The outer frame may include an anchor support strut extending between a downstream junction of the outer frame and a point of connection between one of the tissue anchors and the outer frame. The anchor support strut may be configured for placement parallel to a longitudinal axis of the prosthetic valve.

CROSS-REFERENCES TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No. 15/541,783, filed Jul. 6, 2017, now pending, which is a U.S. national stage entry under 35 U.S.C. § 371 of International Application No. PCT/IL2016/050125, filed Feb. 3, 2016, which claims priority from U.S. Provisional Patent Application No. 62/112,343, filed Feb. 5, 2015, all of which are hereby incorporated by reference in their entirety. This application also claims priority from U.S. Provisional Patent Application No. 62/560,384, filed Sep. 19, 2017, which is hereby incorporated by reference in its entirety.

FIELD OF THE INVENTION

Some embodiments of the present invention relate in general to valve replacement. More specifically, some embodiments of the present invention relate to prosthetic valves for replacement of a cardiac valve.

BACKGROUND

Ischemic heart disease causes regurgitation of a heart valve by the combination of ischemic dysfunction of the papillary muscles, and the dilatation of the ventricle that is present in ischemic heart disease, with the subsequent displacement of the papillary muscles and the dilatation of the valve annulus.

Dilatation of the annulus of the valve prevents the valve leaflets from fully coapting when the valve is closed. Regurgitation of blood from the ventricle into the atrium results in increased total stroke volume and decreased cardiac output, and ultimate weakening of the ventricle secondary to a volume overload and a pressure overload of the atrium.

SUMMARY OF THE INVENTION

For some embodiments of the present invention, an implant is provided having a tubular portion, an upstream support portion and one or more flanges. The implant is percutaneously deliverable to a native heart valve in a compressed state, and is expandable at the native valve. The implant and its delivery system facilitate causing the upstream support portion and the flanges to protrude radially outward from the tubular portion without expanding the tubular portion. Expansion of the tubular portion brings the upstream support portion and the flanges closer together, for securing the implant at the native valve by sandwiching tissue of the native valve between the upstream support portion and the flanges.

In accordance with an embodiment of the present invention, an apparatus is provided for use with a native valve that is disposed between an atrium and a ventricle of a heart of a subject, the apparatus including: a valve frame, including a tubular portion that circumscribes a longitudinal axis of the valve frame so as to define a lumen along the axis, the tubular portion defining a plurality of valve-frame coupling elements disposed circumferentially around the longitudinal axis; a plurality of prosthetic leaflets, coupled to the frame, disposed within the lumen, and arranged to provide unidirectional flow of blood from an upstream end of the lumen to a downstream end of the lumen; an outer frame: including a ring defined by a pattern of alternating peaks and troughs, the peaks being longitudinally closer to the upstream end than to the downstream end, and the troughs being longitudinally closer to the downstream end than to the upstream end, and the pattern of the ring having an amplitude longitudinally between the peaks and the troughs, including a plurality of legs, each of the legs coupled to the ring at a respective trough, and shaped to define a plurality of outer-frame coupling elements, each of the outer-frame coupling elements (i) coupled to the ring at a respective peak, and (ii) fixed with respect to a respective valve-frame coupling element, and: the tubular portion has (i) a compressed state in which the tubular portion has a compressed diameter, and (ii) an expanded state in which the tubular portion has an expanded diameter that is greater than the compressed diameter, and the fixation of the outer-frame coupling elements to the valve-frame coupling elements is such that compression of the tubular portion from the expanded state toward the compressed state such that the valve-frame coupling elements pull the outer-frame coupling elements radially inward: (i) reduces a circumferential distance between each of the outer-frame coupling elements and its adjacent outer-frame coupling elements, and (ii) increases the amplitude of the pattern of the ring.

In an embodiment, the ring circumscribes the tubular portion.

In an embodiment, the valve-frame coupling elements are disposed circumferentially around the longitudinal axis between the upstream end and the downstream end but not at the upstream end nor at the downstream end.

In an embodiment, the upstream support portion includes one or more fabric pockets disposed circumferentially, each pocket of the one or more pockets having an opening that faces a downstream direction.

In an embodiment, the outer frame is coupled to the valve frame only via the fixation of the outer-frame coupling elements to the respective valve-frame coupling elements.

In an embodiment, the apparatus further includes an upstream support portion that includes a plurality of arms that extend radially from the tubular portion, and the upstream support portion has (i) a constrained-arm state, and (ii) a released-arm state in which the arms extend radially outward from the tubular portion, each leg has a tissue-engaging flange that has (i) a constrained-flange state, and (ii) a released-flange state in which the flange extends radially outward from the tubular portion, and the apparatus has an intermediate state in which (i) the tubular portion is in its compressed state, (ii) the upstream support portion is in its released-arm state, and (iii) the legs are in their released-flange state.

In an embodiment, the apparatus includes an implant that includes the valve frame, the leaflets, and the outer frame, and the apparatus further includes a tool: including a delivery capsule dimensioned (i) to house and retain the implant in a compressed state of the implant in which (a) the tubular portion is in its compressed state, (b) the upstream support portion is in its constrained-arm state, and (c) the legs are in their constrained-flange state, and (ii) to be advanced percutaneously to the heart of the subject while the implant is housed and in its compressed state, and operable from outside the subject to: transition the implant from its compressed state into the intermediate state while retaining the tubular portion in its compressed state, and subsequently, expand the tubular portion toward its expanded state.

In an embodiment, the tool is operable from outside the subject to transition the implant from its compressed state into the intermediate state by (i) releasing the legs into their released-flange state, while retaining the tubular portion in its compressed state, and (ii) subsequently, releasing the upstream support portion into its released-arm state, while retaining the tubular portion in its compressed state.

In an embodiment, the tool is operable from outside the subject to transition the implant from its compressed state into the intermediate state by (i) releasing the upstream support portion into its released-arm state, while retaining the tubular portion in its compressed state, and (ii) subsequently, releasing the legs into their released-flange state, while retaining the tubular portion in its compressed state.

In an embodiment, the fixation of the outer-frame coupling elements to the valve-frame coupling elements is such that, when the apparatus is in its intermediate state, expansion of the tubular portion from its compressed state toward its expanded state moves the flanges longitudinally away from the valve-frame coupling elements.

In an embodiment, the fixation of the outer-frame coupling elements to the valve-frame coupling elements is such that, when the apparatus is in its intermediate state, expansion of the tubular portion from a compressed state toward an expanded state reduces the amplitude of the pattern of the ring and passes the flanges between the arms.

In an embodiment, the upstream support portion further includes a covering that covers the arms to form an annular shape in the released-arm state, and, when the apparatus is in its intermediate state, expansion of the tubular portion from its compressed state toward its expanded state presses the flanges onto the covering.

In an embodiment, in the compressed state of the tubular portion, a downstream end of each leg of the tubular portion is longitudinally closer than the valve-frame coupling elements to the downstream end, and the flange of each leg is disposed longitudinally closer than the valve-frame coupling elements to the upstream end.

In an embodiment, in the expanded state of the tubular portion, the downstream end of each leg is longitudinally closer than the valve-frame coupling elements to the downstream end, and the flange of each leg is disposed longitudinally closer than the valve-frame coupling elements to the upstream end.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve of a heart of a subject is provided, the apparatus having an implant that includes: a valve frame that includes a tubular portion that circumscribes a longitudinal axis of the valve frame so as to define a lumen along the axis, the tubular portion having an upstream end, a downstream end, a longitudinal length therebetween, and a diameter transverse to the longitudinal axis; a valve member, coupled to the tubular portion, disposed within the lumen, and arranged to provide unidirectional upstream-to-downstream flow of blood through the lumen; an upstream support portion, coupled to the tubular portion; and an outer frame, coupled to the tubular portion, and including a tissue-engaging flange, and: the implant has a first state and a second state, in both the first state and the second state, (i) the upstream support portion extends radially outward from the tubular portion, and (ii) the tissue-engaging flange extends radially outward from the tubular portion, and the tubular portion, the upstream support portion, and the outer frame are arranged such that transitioning of the implant from the first state toward the second state: increases the diameter of the tubular portion by a diameter-increase amount, decreases the length of the tubular portion by a length-decrease amount, and moves the flange a longitudinal distance toward or toward-and-beyond the upstream support portion, the distance being greater than the length-decrease amount.

In an embodiment of the present invention, the tubular portion, the upstream support portion, and the outer frame may be arranged such that the longitudinal distance is more than 20 percent greater than the length-decrease amount.

In an embodiment, the tubular portion, the upstream support portion, and the outer frame may be arranged such that the longitudinal distance is more than 30 percent greater than the length-decrease amount.

In an embodiment, the tubular portion, the upstream support portion, and the outer frame may be arranged such that the longitudinal distance is more than 40 percent greater than the length-decrease amount.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve that is disposed between an atrium and a ventricle of a heart of a subject is provided, the apparatus including: a valve frame, including a tubular portion that circumscribes a longitudinal axis of the valve frame so as to define a lumen along the axis; a plurality of prosthetic leaflets, coupled to the frame, disposed within the lumen, and arranged to provide unidirectional flow of blood from an upstream end of the lumen to a downstream end of the lumen; an outer frame, including: a ring defined by a pattern of alternating peaks and troughs: the peaks being longitudinally closer than the troughs to the upstream end, the peaks being fixed to respective sites of the tubular portion at respective coupling points disposed circumferentially around the longitudinal axis, and the pattern of the ring having an amplitude longitudinally between the peaks and the troughs; and a plurality of legs, each of the legs coupled to the ring at a respective trough, and: the tubular portion has (i) a compressed state in which the tubular portion has a compressed diameter, and (ii) an expanded state in which the tubular portion has an expanded diameter that is greater than the compressed diameter, and the fixation of the peaks to the respective sites of the tubular portion is such that compression of the tubular portion from the expanded state toward the compressed state such that the respective sites of the tubular portion pull the peaks radially inward via radially-inward tension on the coupling points: (i) reduces a circumferential distance between each of the coupling points and its adjacent coupling points, and (ii) increases the amplitude of the pattern of the ring.

In an embodiment, the outer frame may be coupled to the valve frame only via the fixation of the peaks to the respective sites of the tubular portion at the respective coupling points.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve that is disposed between an atrium and a ventricle of a heart of a subject is provided, the apparatus including: a valve frame, including a tubular portion that circumscribes a longitudinal axis of the valve frame so as to define a lumen along the axis, the valve frame defining a plurality of valve-frame coupling elements disposed circumferentially around the longitudinal axis; a plurality of prosthetic leaflets, coupled to the frame, disposed within the lumen, and arranged to provide unidirectional flow of blood from an upstream end of the lumen to a downstream end of the lumen; an outer frame: including a ring defined by a pattern of alternating peaks and troughs, the peaks being longitudinally closer to the upstream end than to the downstream end, and the troughs being longitudinally closer to the downstream end than to the upstream end, and the pattern of the ring having an amplitude longitudinally between the peaks and the troughs, including a plurality of legs, each of the legs coupled to the ring at a respective trough, and shaped to define a plurality of outer-frame coupling elements, each of the outer-frame coupling elements (i) coupled to the ring at a respective peak, and (ii) fixed with respect to a respective valve-frame coupling element, and: the tubular portion has (i) a compressed state in which the tubular portion has a compressed diameter, and (ii) an expanded state in which the tubular portion has an expanded diameter that is greater than the compressed diameter, and the fixation of the outer-frame coupling elements with respect to the valve-frame coupling elements is such that compression of the tubular portion from the expanded state toward the compressed state (i) pulls the outer-frame coupling elements radially inward via radially-inward pulling of the valve-frame coupling elements on the outer-frame coupling elements, (ii) reduces a circumferential distance between each of the outer-frame coupling elements and its adjacent outer-frame coupling elements, and (iii) increases the amplitude of the pattern of the ring, without increasing a radial gap between the valve frame and the ring by more than 1.5 mm.

In an embodiment, the outer frame may be coupled to the valve frame only via the fixation of the outer-frame coupling elements to the respective valve-frame coupling elements.

There is further provided, in accordance with an embodiment of the present invention, an apparatus for use with a native valve that is disposed between an atrium and a ventricle of a heart of a subject is provided, the apparatus including: a valve frame, including a tubular portion that circumscribes a longitudinal axis of the valve frame so as to define a lumen along the axis; a plurality of prosthetic leaflets, coupled to the frame, disposed within the lumen, and arranged to provide unidirectional flow of blood from an upstream end of the lumen to a downstream end of the lumen; an outer frame, including: a ring defined by a pattern of alternating peaks and troughs: the peaks being longitudinally closer than the troughs to the upstream end, the peaks being fixed to respective sites of the tubular portion at respective coupling points disposed circumferentially around the longitudinal axis, and the pattern of the ring having an amplitude longitudinally between the peaks and the troughs; and a plurality of legs, each of the legs coupled to the ring at a respective trough, and: the tubular portion has (i) a compressed state in which the tubular portion has a compressed diameter, and (ii) an expanded state in which the tubular portion has an expanded diameter that is greater than the compressed diameter, and the fixation of the peaks to the respective sites of the tubular portion is such that compression of the tubular portion from the expanded state toward the compressed state (i) pulls the peaks radially inward via radially-inward pulling of the respective sites of the tubular portion on the peaks, (ii) reduces a circumferential distance between each of the coupling points and its adjacent coupling points, and (iii) increases the amplitude of the pattern of the ring, without increasing a radial gap between the valve frame and the ring by more than 1.5 mm.

In an embodiment, the outer frame may be coupled to the valve frame only via the fixation of the peaks to the respective sites of the tubular portion at the respective coupling points.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve disposed between an atrium and a ventricle of a heart of a subject is provided, the apparatus including: a valve frame, including a tubular portion that circumscribes a longitudinal axis of the valve frame so as to define a lumen along the axis, the tubular portion having an upstream end, a downstream end, and defining a plurality of valve-frame coupling elements disposed circumferentially around the longitudinal axis between the upstream end and the downstream end but not at the upstream end nor at the downstream end; a plurality of prosthetic leaflets, disposed within the lumen, and arranged to provide unidirectional flow of blood through the lumen; an outer frame: including a ring defined by a pattern of alternating peaks and troughs, the peaks being longitudinally closer to the upstream end than to the downstream end, and the troughs being longitudinally closer to the downstream end than to the upstream end, including a plurality of legs, each of the legs coupled to the ring at a respective trough, and shaped to define a plurality of outer-frame coupling elements, each of the outer-frame coupling elements (i) coupled to the ring at a respective peak, and (ii) fixed with respect to a respective valve-frame coupling element at a respective coupling point, and: the tubular portion has (i) a compressed state in which the tubular portion has a compressed diameter, and (ii) an expanded state in which the tubular portion has an expanded diameter that is greater than the compressed diameter, and expansion of the tubular portion from the compressed state toward the expanded state (i) increases a circumferential distance between each of the outer-frame coupling elements and its adjacent outer-frame coupling elements, and (ii) moves the plurality of legs in a longitudinally upstream direction with respect to the tubular portion.

In an embodiment, the outer frame may be coupled to the valve frame only via the fixation of the outer-frame coupling elements to the respective valve-frame coupling elements.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve disposed between an atrium and a ventricle of a heart of a subject is provided, the apparatus including: a valve frame, including a tubular portion that circumscribes a longitudinal axis of the valve frame so as to define a lumen along the axis, the tubular portion having an upstream end and a downstream end; a plurality of prosthetic leaflets, disposed within the lumen, and arranged to provide unidirectional flow of blood through the lumen; an outer frame, including: a ring defined by a pattern of alternating peaks and troughs: the peaks being longitudinally closer than the troughs to the upstream end, the peaks being fixed to respective sites of the tubular portion at respective coupling points disposed circumferentially around the longitudinal axis between the upstream end and the downstream end but not at the upstream end nor the downstream end; and a plurality of legs, each of the legs coupled to the ring at a respective trough, and: the tubular portion has (i) a compressed state in which the tubular portion has a compressed diameter, and (ii) an expanded state in which the tubular portion has an expanded diameter that is greater than the compressed diameter, and expansion of the tubular portion from the compressed state toward the expanded state (i) increases a circumferential distance between each of the coupling points and its adjacent coupling points, and (ii) moves the plurality of legs in a longitudinally upstream direction with respect to the tubular portion.

In an embodiment, the outer frame may be coupled to the valve frame only via the fixation of the peaks to the respective sites of the tubular portion at the respective coupling points.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve of a heart of a subject is provided, the apparatus including: a frame assembly, having an upstream end and a downstream end, and a central longitudinal axis therebetween, and including: a valve frame, including: a tubular portion having an upstream end and a downstream end, and shaped to define a lumen therebetween, and an upstream support portion, extending from the upstream end of the tubular portion; and at least one leg, coupled to the valve frame at a coupling point, and having a tissue-engaging flange; and a valve member disposed within the lumen, and configured to facilitate one-way liquid flow through the lumen from the upstream end of the tubular portion to the downstream end of the tubular portion, and the frame assembly: has a compressed state, for percutaneous delivery to the heart, in which the tubular portion has a compressed diameter, is biased to assume an expanded state in which the tubular portion has an expanded diameter that is greater than the compressed diameter, and is configured such that increasing the diameter of the tubular portion toward the expanded diameter causes longitudinal movement: of the upstream support portion toward the coupling point, and of the tissue-engaging flange away from the coupling point.

In an embodiment: the apparatus includes an implant that includes the frame assembly and the valve member, and the apparatus further includes a tool: including a delivery capsule dimensioned (i) to house and retain the implant in the compressed state, and (ii) to be advanced percutaneously to the heart of the subject while the implant is housed and in the compressed state, and operable from outside the subject to facilitate an increase of the diameter of the tubular portion from the compressed diameter toward the expanded diameter such that the increase of the diameter actuates longitudinal movement: of the upstream support portion toward the coupling point, and of the tissue-engaging flange away from the coupling point.

In an embodiment, the frame assembly may be configured such that increasing the diameter of the tubular portion by expanding the frame assembly toward the expanded state causes longitudinal movement of the upstream end of the tubular portion toward the coupling point.

In an embodiment, the coupling point is disposed closer to the downstream end of the frame assembly than are either the tissue-engaging flange or the upstream support portion.

In an embodiment, in the expanded state of the frame assembly, the leg extends away from the central longitudinal axis.

In an embodiment, the expanded state of the frame assembly may be a fully-expanded state of the frame assembly, the leg is expandable into an expanded state of the leg, independently of increasing the diameter of the tubular portion, and in the expanded state of the leg, the leg extends away from the central longitudinal axis.

In an embodiment, in the expanded state of the frame assembly, the leg extends away from the central longitudinal axis, and in the compressed state of the frame assembly, the leg is generally parallel with the central longitudinal axis.

In an embodiment, the frame assembly may be configured such that the longitudinal movement of the tissue-engaging flange away from the coupling point is a translational movement of the tissue-engaging flange that does not include rotation of the tissue-engaging flange.

In an embodiment, the frame assembly may be configured such that increasing the diameter of the tubular portion by expanding the frame assembly toward the expanded state causes 1-20 mm of longitudinal movement of the tissue-engaging flange away from the coupling point.

In an embodiment, the frame assembly may be configured such that increasing the diameter of the tubular portion by expanding the frame assembly toward the expanded state causes 1-20 mm of longitudinal movement of the upstream support portion toward the coupling point.

In an embodiment, the frame assembly may be configured such that increasing the diameter of the tubular portion by expanding the frame assembly toward the expanded state reduces a distance between the upstream support portion and the tissue-engaging flange by 5-30 mm.

In an embodiment, the frame assembly may be configured such that increasing the diameter of the tubular portion by expanding the frame assembly toward the expanded state moves the tissue-engaging flange longitudinally past the upstream support portion.

In an embodiment, the tubular portion may be defined by a plurality of cells of the valve frame, and increasing the diameter of the tubular portion by expanding the frame assembly toward the expanded state: includes (i) increasing a width, orthogonal to the longitudinal axis of the frame assembly, of each cell, and (ii) reducing a height, parallel with the longitudinal axis of the frame assembly, of each cell, and causes longitudinal movement of the upstream support portion toward the coupling point by reducing a height, parallel with the longitudinal axis of the frame assembly, of the tubular portion, by reducing the height of each cell.

In an embodiment, the leg is disposed on an outside of the tubular portion.

In an embodiment, the at least one leg includes a plurality of legs, the coupling point includes a plurality of coupling points, and the frame assembly includes a leg frame that circumscribes the tubular portion, includes the plurality of legs, and is coupled to the valve frame at the plurality of coupling points, such that the plurality of legs is distributed circumferentially around the tubular portion.

In an embodiment, the plurality of coupling points is disposed circumferentially around the frame assembly on a transverse plane that is orthogonal to the longitudinal axis of the frame assembly.

In an embodiment, the plurality of legs may be coupled to the valve frame via a plurality of struts, each strut having a first end that is coupled to a leg of the plurality of legs, and a second end that is coupled to a coupling point of the plurality of coupling points, in the compressed state of the frame assembly, being disposed at a first angle in which the first end is disposed closer to the downstream end of the frame assembly than is the second end, and being deflectable with respect to the coupling point of the plurality of coupling points, such that increasing the diameter of the tubular portion by expanding the frame assembly toward the expanded state causes the strut to deflect to a second angle in which the first end is disposed further from the downstream end of the frame assembly than is the first end in the compressed state of the frame assembly.

In an embodiment, the leg frame may be structured such that each leg of the plurality of legs is coupled to two struts of the plurality of struts, and two struts of the plurality of struts are coupled to each coupling point of the plurality of coupling points.

In an embodiment, the leg may be coupled to the valve frame via a strut, the strut having a first end that is coupled to the leg, and a second end that is coupled to the coupling point, in the compressed state of the frame assembly, being disposed at a first angle in which the first end is disposed closer to the downstream end of the frame assembly than is the second end, and being deflectable with respect to the coupling point, such that increasing the diameter of the tubular portion by expanding the frame assembly toward the expanded state causes the strut to deflect to a second angle in which the first end is disposed further from the downstream end of the frame assembly than is the first end in the compressed state of the frame assembly.

In an embodiment, the at least one leg includes at least a first leg and a second leg.

In an embodiment, the first leg and the second leg are both coupled to the valve frame at the coupling point.

In an embodiment, the first leg may be coupled to the coupling point via a respective first strut, and the second leg is coupled to the coupling point via a respective second strut.

In an embodiment, the first and second legs, the first and second struts, and the coupling point are arranged such that, in the expanded state of the frame assembly: the coupling point is disposed, circumferentially with respect to the tubular portion, between the first strut and the second strut, the first strut is disposed, circumferentially with respect to the tubular portion, between the coupling point and the first leg, and the second strut is disposed, circumferentially with respect to the tubular portion, between the coupling point and the second leg.

In an embodiment, the coupling point includes at least a first coupling point and a second coupling point.

In an embodiment, the leg is coupled to the valve frame at the first coupling point and at the second coupling point.

In an embodiment, the leg may be coupled to the first coupling point via a respective first strut, and to the second coupling point via a respective second strut.

In an embodiment, the first and second legs, the first and second struts, and the coupling point are arranged such that, in the expanded state of the frame assembly: the leg is disposed, circumferentially with respect to the tubular portion, between the first strut and the second strut, the first strut is disposed, circumferentially with respect to the tubular portion, between the leg and the first coupling point, and the second strut is disposed, circumferentially with respect to the tubular portion, between the leg and the second coupling point.

In an embodiment, in the expanded state of the frame assembly, the upstream support portion extends radially outward from the tubular portion.

In an embodiment, the expanded state of the frame assembly is a fully-expanded state of the frame assembly, the upstream support portion is expandable into an expanded state of the upstream support portion, independently of increasing the diameter of the tubular portion, and in the expanded state of the upstream support portion, the upstream support portion extends radially outward from the tubular portion.

In an embodiment, in the compressed state of the frame assembly, the upstream support portion is generally tubular, collinear with the tubular portion, and disposed around the central longitudinal axis.

In an embodiment, in the expanded state of the frame assembly, an inner region of the upstream support portion extends radially outward from the tubular portion at a first angle with respect to the tubular portion, and an outer region of the upstream support portion extends, from the inner region of the upstream support portion, further radially outward from the tubular portion at a second angle with respect to the tubular portion, the second angle being smaller than the first angle.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve of a heart of a subject is provided, the apparatus including a frame assembly, having an upstream end and a downstream end, and a central longitudinal axis therebetween, and including: a valve frame, including: a tubular portion having an upstream end and a downstream end, and shaped to define a lumen therebetween, and an upstream support portion, extending from the upstream end of the tubular portion; and at least one leg, coupled to the valve frame at a coupling point, and having a tissue-engaging flange; and a valve member disposed within the lumen, and configured to facilitate one-way liquid flow through the lumen from the upstream end of the tubular portion to the downstream end of the tubular portion, and the frame assembly: has a compressed state, for percutaneous delivery to the heart, in which the tubular portion has a compressed diameter, is biased to assume an expanded state in which the tubular portion has an expanded diameter that is greater than the compressed diameter, and is configured such that reducing the diameter of the tubular portion toward the compressed diameter causes longitudinal movement of the upstream support portion away from the coupling point, and of the tissue-engaging flange toward the coupling point.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve of a heart of a subject is provided, the apparatus including a frame assembly, having an upstream end and a downstream end, and a central longitudinal axis therebetween, including: a valve frame, including: a tubular portion having an upstream end and a downstream end, and shaped to define a lumen therebetween, and an upstream support portion, extending from the upstream end of the tubular portion; and at least one leg, coupled to the valve frame at a coupling point, and having a tissue-engaging flange; and a valve member disposed within the lumen, and configured to facilitate one-way liquid flow through the lumen from the upstream end of the tubular portion to the downstream end of the tubular portion, and the frame assembly: has a compressed state, for percutaneous delivery to the heart, is intracorporeally expandable into an expanded state in which a diameter of the tubular portion is greater than in the compressed state, and is configured such that increasing the diameter of the tubular portion by expanding the frame assembly toward the expanded state causes longitudinal movement of the tissue-engaging flange away from the coupling point.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve of a heart of a subject is provided, the apparatus including a frame assembly, having an upstream end and a downstream end, and a central longitudinal axis therebetween, and including: an inner frame including an inner-frame tubular portion that circumscribes the central longitudinal axis, has an upstream end and a downstream end, and defines a channel therebetween, the inner frame defining a plurality of inner-frame couplings disposed circumferentially at a longitudinal location of the inner frame, an outer frame including an outer-frame tubular portion that coaxially circumscribes at least a portion of the inner-frame tubular portion, the outer frame defining a plurality of outer-frame couplings disposed circumferentially at a longitudinal location of the outer frame, and a plurality of connectors, each connector connecting a respective inner-frame coupling to a respective outer-frame coupling; a liner, disposed over at least part of the inner-frame tubular portion; and a plurality of prosthetic leaflets, coupled to the inner-frame tubular portion and disposed within the channel, and: the frame assembly: (i) is compressible by a radially-compressive force into a compressed state in which the inner frame is in a compressed state thereof and the outer frame is in a compressed state thereof, (ii) is configured, upon removal of the radially-compressive force, to automatically expand into an expanded state thereof in which the inner frame is in an expanded state thereof and the outer frame is in an expanded state thereof, in the expanded state of the frame assembly, the prosthetic leaflets are configured to facilitate one-way fluid flow, in a downstream direction, through the channel, and the connection of the inner-frame couplings to the respective outer-frame couplings is such that expansion of the frame assembly from the compressed state to the expanded state causes the inner-frame tubular portion to slide longitudinally in a downstream direction with respect to the outer-frame tubular portion.

In accordance with an embodiment of the present invention, an apparatus for use with a native valve disposed between an atrium and a ventricle of a heart of a subject is provided, the apparatus including: a tubular portion, having an upstream portion that includes an upstream end, and a downstream portion that includes a downstream end, and shaped to define a lumen between the upstream portion and the downstream portion; a plurality of prosthetic leaflets, disposed within the lumen, and arranged to provide unidirectional flow of blood from the upstream portion to the downstream portion; an annular upstream support portion: having an inner portion that extends radially outward from the upstream portion, and including one or more fabric pockets disposed circumferentially around the inner portion, each pocket of the one or more pockets having an opening that faces a downstream direction.

In an embodiment, the upstream support portion includes (i) a plurality of arms that extend radially outward from the tubular portion, and (ii) a covering, disposed over the plurality of arms, each arm has (i) a radially-inner part at the inner portion of the upstream support portion, and (ii) a radially-outer part at the outer portion of the upstream support portion, at the inner portion of the upstream support portion, the covering is closely-fitted between the radially-inner parts of the arms, and at the outer portion of the upstream support portion, the pockets are formed by the covering being loosely-fitted between the radially-outer parts of the arms.

In an embodiment, the upstream support portion includes (i) a plurality of arms that extend radially outward from the tubular portion, and (ii) a covering, disposed over the plurality of arms, each arm has (i) a radially-inner part at the inner portion of the upstream support portion, and (ii) a radially-outer part at the outer portion of the upstream support portion, the radially-outer part being more flexible than the radially-inner part.

In an embodiment, the upstream support portion includes (i) a plurality of arms that extend radially outward from the tubular portion, and (ii) a covering, disposed over the plurality of arms, each arm has (i) a radially-inner part at the inner portion of the upstream support portion, and (ii) a radially-outer part at the outer portion of the upstream support portion, at the outer portion of the upstream support portion, the pockets are formed by each arm curving to form a hook shape.

In an embodiment, each pocket may be shaped and arranged to billow in response to perivalvular flow of blood in an upstream direction.

In an embodiment, the apparatus may be configured to be transluminally delivered to the heart and implanted at the native valve by expansion of the apparatus, such that the upstream support portion is disposed in the atrium and the tubular portion extends from the upstream support portion into the ventricle, and each pocket is shaped and arranged such that perivalvular flow of blood in an upstream direction presses the pocket against tissue of the atrium.

In accordance with an embodiment of the present invention, an apparatus is provided including a plurality of prosthetic valve leaflets; and a frame assembly, including: a tubular portion defined by a repeating pattern of cells, the tubular portion extending circumferentially around a longitudinal axis so as to define a longitudinal lumen, the prosthetic valve leaflets coupled to the inner frame and disposed within the lumen; an outer frame, including a plurality of legs, distributed circumferentially around the tubular portion, each leg having a tissue-engaging flange; an upstream support portion that includes a plurality of arms that extend radially outward from the tubular portion; and a plurality of appendages, each having a first end that defines a coupling element via which the tubular portion is coupled to the outer frame, and a second end; and the frame assembly defines a plurality of hubs, distributed circumferentially around the longitudinal axis on a plane that is transverse to the longitudinal axis, each hub defined by convergence and connection of, (i) two adjacent cells of the tubular portion, (ii) an arm of the plurality of arms, and (iii) an appendage of the plurality of appendages.

In an embodiment, each hub has six radiating spokes, two of the six spokes being part of a first cell of the two adjacent cells, two of the six spokes being part of a second cell of the two adjacent cells, one of the six spokes being the arm, and one of the six spokes being the second end of the appendage.

In an embodiment, the appendages are in-plane with the tubular portion.

In an embodiment, the appendages are in-plane with the outer frame.

In accordance with an embodiment of the present invention, a method for use with a native valve of a heart of a subject is provided, the method including percutaneously advancing to heart, an implant: including a valve frame, a valve member disposed within a lumen defined by the valve frame, and at least one leg, coupled to the valve frame at a coupling point, and having an upstream end, a downstream end, and a central longitudinal axis therebetween; positioning the implant within the heart such that a tissue-engaging flange of the leg is disposed downstream of the valve, and thereafter causing the flange to protrude radially outward from the axis; subsequently, while an upstream support portion of the valve frame is disposed upstream of the valve, causing the upstream support portion to protrude radially outward from the axis, such that tissue of the valve is disposed between the upstream support portion and the flange; and subsequently, sandwiching the tissue between the upstream support portion and the flange by reducing a distance between the upstream support portion and the flange by causing longitudinal movement (i) of the upstream support portion toward the coupling point, and (ii) of the tissue-engaging flange away from the coupling point.

In an embodiment, causing the longitudinal movement (i) of the upstream support portion toward the coupling point, and (ii) of the tissue-engaging flange away from the coupling point, includes causing the longitudinal movement by increasing a diameter of the lumen.

In accordance with an embodiment of the present invention, a method for use with a native valve of a heart of a subject is provided, the method including percutaneously advancing to heart, an implant: including a valve frame, a valve member disposed within a lumen defined by the valve frame, and at least one leg, coupled to the valve frame at a coupling point, and having an upstream end, a downstream end, and a central longitudinal axis therebetween; positioning the implant within the heart such that an upstream support portion of the valve frame is disposed upstream of the valve, and thereafter causing the upstream support portion to protrude radially outward from the axis; subsequently, while a tissue-engaging flange of the leg is disposed downstream of the valve, causing the tissue-engaging flange to protrude radially outward from the axis, such that tissue of the valve is disposed between the upstream support portion and the flange; and subsequently, sandwiching the tissue between the upstream support portion and the flange by reducing a distance between the upstream support portion and the flange by causing longitudinal movement (i) of the upstream support portion toward the coupling point, and (ii) of the tissue-engaging flange away from the coupling point.

In an embodiment, causing the longitudinal movement (i) of the upstream support portion toward the coupling point, and (ii) of the tissue-engaging flange away from the coupling point, includes causing the longitudinal movement by increasing a diameter of the lumen.

In accordance with an embodiment of the present invention, a method for use with a native valve of a heart of a subject is provided, the method including: percutaneously advancing an implant to the heart, the implant having an upstream end, a downstream end, and a central longitudinal axis therebetween, and including a tubular portion, an upstream support portion, and a plurality of tissue-engaging flanges; positioning the implant within the heart such that the upstream support portion is disposed upstream of the valve, positioning the implant within the heart such that the tissue-engaging flanges are disposed downstream of the valve, without increasing a diameter of the tubular portion: causing the upstream support portion to extend radially outward from the axis so as to have a first support-portion span, and causing the flanges to extend radially outward from the axis so as to have a first flange span; and subsequently, causing the upstream support portion and the flanges move toward each other by at least 5 mm by increasing a diameter of the tubular portion such that: the upstream support portion extends radially outward so as to have a second support-portion span, the first support-portion span being at least 40 percent as great as the second support-portion span, and the flanges extend radially outward so as to have a second flange span, the first flange span being at least 30 percent as great as the second flange span.

There is further provided, in accordance with an application of the present invention, a method for use with a native valve of a heart of a subject, the method including: percutaneously advancing an implant to the heart, the implant: having an upstream end, a downstream end, and a central longitudinal axis therebetween, and including a tubular portion, an upstream support portion, and a plurality of tissue-engaging flanges; positioning the implant within the heart such that the upstream support portion is disposed upstream of the valve, positioning the implant within the heart such that the tissue-engaging flanges are disposed downstream of the valve, without increasing a diameter of the tubular portion: causing the upstream support portion to extend radially outward from the axis, and causing the flanges to extend radially outward from the axis so as to have a first flange span; and subsequently, by increasing a diameter of the tubular portion: causing the upstream support portion and the flanges move toward each other by at least 5 mm, causing the upstream support portion to move further radially outward from the axis, and causing each flange of the plurality of flanges to translate radially outward so as to have a second flange span that is greater than the first flange span.

The present invention will be more fully understood from the following detailed description of applications thereof, taken together with the drawings, in which:

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A-B and 2A-E are schematic illustrations of an implant for use with a native valve of a heart of a subject, in accordance with some applications of the invention;

FIGS. 3A-C are schematic illustrations that show structural changes in a frame assembly during transitioning of the assembly between its compressed and expanded states, in accordance with some applications of the invention;

FIGS. 4A-F are schematic illustrations of implantation of the implant at the native valve, in accordance with some applications of the invention;

FIG. 5 is a schematic illustration of a step in the implantation of the implant, in accordance with some applications of the invention;

FIG. 6 is a schematic illustration of the implant, in accordance with some applications of the invention;

FIGS. 7A-B and 8A-B are schematic illustrations of frame assemblies of respective implants, in accordance with some applications of the invention; and

FIGS. 9A-C are schematic illustrations of an implant comprising a frame assembly, in accordance with some applications of the invention.

DETAILED DESCRIPTION OF EMBODIMENTS

Reference is made to FIGS. 1A-B and 2A-E, which are schematic illustrations of an implant 20 (alternatively, “prosthetic valve 20”) for use with a native valve of a heart of a subject, in accordance with some embodiments of the invention. Prosthetic valve 20 comprises a frame assembly 22 that has an upstream end 24 (alternatively, “atrial end 24”), a downstream end 26 (alternatively, “ventricular end 26”), and a central longitudinal axis ax1 therebetween. The term “atrial end” may refer to an end of a given feature which is configured to be situated closest to an atrium of the heart when prosthetic valve 20 is implanted therein. For example, in FIG. 1A, the atrial end of prosthetic valve 20 may be the top end of prosthetic valve 20. Similarly, the term “ventricular end” may refer to an end of a given feature which is configured to be situated closest to a ventricle of the heart when prosthetic valve 20 is implanted therein. For example, in FIGS. 2A-2E, the ventricular end of prosthetic valve 20 may be the bottom end of prosthetic valve 20. Frame assembly 22 comprises a valve frame 30 (alternatively “inner frame 30”) that comprises a tubular portion 32 that has an upstream end 34 (alternatively, “atrial end 34”) and a downstream end 36 (alternatively, “ventricular end 36”), and is shaped to define a lumen 38 through the tubular portion from the atrial end to the ventricular end. Tubular portion 32 circumscribes axis ax1, and thereby defines lumen 38 along the axis. Inner frame 30 further comprises an upstream support portion 40, extending from atrial end 34 of tubular portion 32. Frame assembly 22 further comprises at least one leg 50 (alternatively, “ventricular anchor support 50”), coupled to inner frame 30 at (e.g., via) a coupling point 52, and having a tissue-engaging flange 54 (alternatively, “outer frame tissue anchor 54”).

Typically, and as described hereinbelow, ventricular anchor support 50 is part of an outer frame 60, and frames 30 and 60 define respective coupling elements 31 and 61, which are fixed with respect to each other at coupling points 52. As illustrated in FIG. 1A, inner frame 30 may be positioned at least partially within outer frame 60. Typically, frames 30 and 60 are coupled to each other only at coupling points 52 (e.g., only via the fixation of coupling elements 31 and 61 with respect to each other).

Prosthetic valve 20 further comprises a valve member 58 (e.g., one or more prosthetic leaflets) disposed within lumen 38, and configured to facilitate one-way liquid flow through the lumen from atrial end 34 to ventricular end 36 (e.g., thereby defining the orientation of the upstream and ventricular ends of tubular portion 32). FIG. 1A shows prosthetic valve 20 in a fully-expanded state, in which frame assembly 22 is in a fully-expanded state. FIG. 1B shows an exploded view of frame assembly 22 in its fully-expanded state. FIGS. 2A-E show respective states of prosthetic valve 20, which will be discussed in more detail hereinbelow with respect to the implantation of the implant and the anatomy in which the implant is implanted. FIG. 2A shows prosthetic valve 20 in a compressed state (in which frame assembly 22 is in a compressed state), for percutaneous delivery of the implant to the heart of the subject. Typically, in the compressed state, ventricular anchor support 50 (including outer frame tissue anchor 54 thereof) is in a constrained-anchor state in which the outer frame tissue anchor is generally parallel with axis ax1. Further typically, in the compressed state, upstream support portion 40 is generally tubular, collinear with tubular portion 32 (e.g., extending collinearly from the tubular portion), and disposed around axis ax1.

FIG. 2B shows a state of prosthetic valve 20 in which outer frame tissue anchor 54 of each ventricular anchor support 50 extends radially away from axis ax1 (e.g., radially away from tubular portion 32). FIG. 2C shows a state of prosthetic valve 20 in which upstream-support portion 40 extends radially away from axis ax1 (and thereby radially away from tubular portion 32). FIG. 2D shows a state of prosthetic valve 20 in which both outer frame tissue anchor 54 and portion 40 extend away from axis ax1. In the fully-expanded state (FIGS. 1A-B) both upstream support portion 40 and outer frame tissue anchor 54 extend radially away from axis ax1. Typically, frame assembly 22 is biased (e.g., shape-set) to assume its fully-expanded state, which is shown in FIG. 2E. Transitioning of prosthetic valve 20 between the respective states is typically controlled by delivery apparatus, such as by constraining the implant in a compressed state within a delivery tube and/or against a control rod, and selectively releasing portions of the implant to allow them to expand.

In the compressed state of frame assembly 22, tubular portion 32 has a diameter d1, and in the expanded state, the tubular portion has a diameter d2 that is greater that diameter d1. For some embodiments, diameter d1 is 4-15 mm, (e.g., 5-11 mm) and diameter d2 is 20-50 mm, (e.g., 23-33 mm). Frame assembly 22 is configured such that increasing the diameter of tubular portion 32 (e.g., from d1 to d2) causes longitudinal movement of outer frame tissue anchor 54 away from coupling point 52. In the same way, reducing the diameter of tubular portion 32 (e.g., from d2 to d1) causes longitudinal movement of outer frame tissue anchor 54 toward coupling point 52. It is to be noted that the term “longitudinal movement” (including the specification and the claims) means movement parallel with central longitudinal axis ax1. Therefore longitudinal movement of outer frame tissue anchor 54 away from coupling point 52 means increasing a distance, measured parallel with longitudinal axis ax1, between outer frame tissue anchor 54 and coupling point 52. An example of such a configuration is described in more detail with respect to FIG. 3A.

Thus, expansion of tubular portion 32 from its compressed state toward its expanded state (i) increases a circumferential distance between each of coupling points 52 and its adjacent coupling points (e.g., between each of outer-frame coupling elements 61 and its adjacent outer-frame coupling elements) (e.g., from d8 to d9), and (ii) moves ventricular anchor support 50 in a longitudinally upstream direction with respect to the tubular portion.

Typically, frame assembly 22 is configured such that increasing the diameter of tubular portion 32 also causes longitudinal movement of upstream support portion 40 toward coupling point 52, e.g., as described in more detail with respect to FIGS. 3B-C. Typically, frame assembly 22 is configured such that increasing the diameter of tubular portion 32 also causes longitudinal movement of atrial end 34 of tubular portion 32 toward coupling point 52. In the same way, reducing the diameter of tubular portion 32 causes longitudinal movement of atrial end 34 away from coupling point 52.

For some embodiments, upstream support portion 40 comprises a plurality of inner frame tissue anchors 46 that each extends radially outward from tubular portion 32 (e.g., from atrial end 34 of the tubular portion). inner frame tissue anchors 46 are typically flexible. For some such embodiments, inner frame tissue anchors 46 are coupled to tubular portion 32 such that each inner frame tissue anchor may deflect independently of adjacent inner frame tissue anchors 46 during implantation (e.g., due to anatomical topography).

For some embodiments, upstream support portion 40 comprises a plurality of barbs 48 that extend out of a downstream surface of the upstream support portion. For example, each inner frame tissue anchor 46 may comprise one or more of barbs 48. Barbs 48 press into tissue upstream of the native valve (e.g., into the valve annulus), thereby inhibiting downstream movement of prosthetic valve 20 (in addition to inhibition of downstream movement provided by the geometry of upstream support portion 40).

One or more surfaces of frame assembly 22 are covered with a covering 23, which typically comprises a flexible sheet, such as a fabric, e.g., comprising polyester. Typically, covering 23 covers at least part of tubular portion 32, typically lining an inner surface of the tubular portion, and thereby defining lumen 38.

Further typically, upstream support portion 40 is covered with covering 23, e.g., extending between inner frame tissue anchors 46 to form an annular shape. It is hypothesized that this reduces a likelihood of paravalvular leakage. For such embodiments, excess covering 23 may be provided between inner frame tissue anchors 46 of upstream support portion 40, so as to facilitate their independent movement. Although FIG. 1A shows covering 23 covering an upstream side of upstream support portion 40, the covering typically additionally (or alternatively) covers the downstream side of the upstream support portion. For example, covering 23 may extend over the tips of inner frame tissue anchors 46 and down the outside of the inner frame tissue anchors, or a separate piece of covering may be provided on the downstream side of the upstream support portion.

Alternatively, each inner frame tissue anchor 46 may be individually covered in a sleeve of covering 23, thereby facilitating independent movement of the inner frame tissue anchors.

For some embodiments, at least a portion of ventricular anchor support 50 (e.g., outer frame tissue anchors 54 thereof) is covered with covering 23.

Typically, frame assembly 22 comprises a plurality of ventricular anchor supports 50 (e.g., two or more ventricular anchor supports, e.g., 2-16 ventricular anchor supports, such as 4-12 ventricular anchor supports, such as 6-12 ventricular anchor supports), arranged circumferentially around inner frame 30 (e.g., around the outside of tubular portion 32). Typically, frame assembly 22 comprises a plurality of coupling points 52 at which the ventricular anchor supports are coupled to inner frame 30.

As described in more detail hereinbelow (e.g., with reference to FIG. 3A), each ventricular anchor support 50 is typically coupled to a coupling point 52 via a strut 70. For some embodiments, each ventricular anchor support 50 is coupled to a plurality of (e.g., two) coupling points 52 via a respective plurality of (e.g., two) struts 70. For some such embodiments, frame assembly 22 is arranged such that, in the expanded state of the frame assembly, ventricular anchor support 50 is disposed, circumferentially with respect to tubular portion 32, between two struts, and each of the two struts are disposed, circumferentially with respect to the tubular portion, between the ventricular anchor support and a respective coupling point 52.

For some embodiments, a plurality of (e.g., two) ventricular anchor supports 50 are coupled to each coupling point 52 via a respective plurality of (e.g., two) struts 70. For some such embodiments, frame assembly 22 is arranged such that, in the expanded state of the frame assembly, coupling point 52 is disposed, circumferentially with respect to tubular portion 32, between two struts 70, and each of the two struts are disposed, circumferentially with respect to the tubular portion, between the coupling point and a respective ventricular anchor support 50.

For some embodiments, frame assembly 22 comprises an outer frame 60 that circumscribes tubular portion 32, comprises (or defines) the plurality of ventricular anchoring supports 50 and the plurality of struts 70, and is coupled to inner frame 30 at the plurality of coupling points 52, such that the plurality of ventricular anchoring supports are distributed circumferentially around the tubular portion. For such embodiments, outer frame 60 comprises a ring 66 that is defined by a pattern of alternating peaks 64 and troughs 62, and that typically circumscribes tubular portion 32. For example, the ring may comprise struts 70, extending between the peaks and troughs. Peaks 64 are longitudinally closer to atrial end 34 of tubular portion 32 than to ventricular end 36, and troughs 62 are longitudinally closer to the ventricular end than to the atrial end. (It is to be noted that throughout this patent application, including the specification and the claims, the term “longitudinally” means with respect to longitudinal axis ax1. For example, “longitudinally closer” means closer along axis ax1 (whether positioned on axis ax1 or lateral to axis ax1), and “longitudinal movement” means a change in position along axis ax1 (which may be in additional to movement toward or away from axis ax1). Therefore, peaks 64 are closer than troughs 62 to atrial end 34, and troughs 62 are closer than peaks 64 to ventricular end 36. For embodiments in which frame 60 comprises ring 66, each ventricular anchor support 50 is coupled to the ring (or defined by frame 60) at a respective trough 62.

In the embodiment shown, the peaks and troughs are defined by ring 66 having a generally zig-zag shape. However, the scope of the invention includes ring 66 having another shape that defines peaks and troughs, such as a serpentine or sinusoid shape.

For embodiments in which frame assembly 22 has a plurality of coupling points 52, the coupling points (and therefore coupling elements 31 and 61) are disposed circumferentially around the frame assembly (e.g., around axis ax1), typically on a transverse plane that is orthogonal to axis ax1. This transverse plane is illustrated by the position of section A-A in FIG. 2B. Alternatively, coupling points 52 may be disposed at different longitudinal heights of frame assembly 22, e.g., such that different outer frame tissue anchors 54 are positioned and/or moved differently to others. Typically, coupling points 52 (and therefore coupling elements 31 and 61) are disposed longitudinally between atrial end 24 and ventricular end 26 of frame assembly 22, but not at either of these ends. Further typically, coupling points 52 are disposed longitudinally between atrial end 34 and ventricular end 36 of tubular portion 32, but not at either of these ends. For example, the coupling points may be more than 3 mm (e.g., 4-10 mm) both from end 34 and from end 36. It is hypothesized that this advantageously positions the coupling points at a part of tubular portion 32 that is more rigid than end 34 or end 36.

It is to be noted that ventricular anchor support 50 is typically expandable into its expanded state (e.g., a released-anchor state) such that outer frame tissue anchor 54 extends away from axis ax1, independently of increasing the diameter of tubular portion 32 (e.g., as shown in FIGS. 2B & 2D). Similarly, upstream support portion 40 is typically expandable into its expanded state (e.g., a released-anchor state) such that it (e.g., inner frame tissue anchors 46 thereof) extends away from axis ax1, independently of increasing the diameter of tubular portion 32 (e.g., as shown in FIGS. 2C & 2D). The state shown in FIG. 2D may be considered to be an intermediate state. Therefore, prosthetic valve 20 is typically configured such that ventricular anchor supports 50 (e.g., outer frame tissue anchors 54 thereof) and upstream support portion 40 are expandable such that they both extend away from axis ax1, while retaining a distance d3 therebetween. This distance is subsequently reducible to a distance d4 by expanding tubular portion 32 (e.g., shown in FIG. 2E).

For some embodiments, while tubular portion 32 remains in its compressed state, outer frame tissue anchor 54 can extend away from axis ax1 over 40 percent (e.g., 40-80 percent, such as 40-70 percent) of the distance that it extends from the axis subsequent to the expansion of the tubular portion. For example, for embodiments in which prosthetic valve 20 comprises a outer frame tissue anchor 54 on opposing sides of the implant, a span d15 of the outer frame tissue anchors while tubular portion 32 is in its compressed state may be at least 40 percent (e.g., 40-80 percent, such as 40-70 percent) as great as a span d16 of the outer frame tissue anchors subsequent to the expansion of the tubular portion. For some embodiments, span d15 is greater than 15 mm and/or less than 50 mm (e.g., 20-30 mm). For some embodiments, span d16 is greater than 30 mm and/or less than 60 mm (e.g., 40-50 mm). It is to be noted that ventricular anchoring support 54 is effectively fully expanded, with respect to other portions of ventricular anchor support 50 and/or with respect to tubular portion 32, before and after the expansion of the tubular portion.

Similarly, for some embodiments, while tubular portion 32 remains in its compressed state, upstream support portion 40 (e.g., inner frame tissue anchors 46) can extend away from axis ax1 over 30 percent (e.g., 30-70 percent) of the distance that it extends from the axis subsequent to the expansion of the tubular portion. That is, for some embodiments, a span d17 of the upstream support portion while tubular portion 32 is in its compressed state may be at least 30 percent (e.g., 30-70 percent) as great as a span d18 of the upstream support portion subsequent to the expansion of the tubular portion. For some embodiments, span d17 is greater than 16 mm (e.g., greater than 20 mm) and/or less than 50 mm (e.g., 30-40 mm). For some embodiments, span d18 is greater than 40 mm and/or less than 65 mm (e.g., 45-56 mm, such as 45-50 mm). It is to be noted that upstream support portion 40 is effectively fully expanded, with respect to tubular portion 32, before and after the expansion of the tubular portion.

It is to be noted that when tubular portion 32 is expanded, outer frame tissue anchors 54 typically translate radially outward from span d15 to span d16 (e.g., without deflecting). Typically upstream support portion 40 behaves similarly (e.g., inner frame tissue anchors 46 translated radially outward from span d17 to span d18, e.g., without deflecting). That is, an orientation of each outer frame tissue anchor 54 and/or each inner frame tissue anchor 46 with respect to tubular portion 32 and/or axis ax1 is typically the same in the state shown in FIG. 2D as it is in the state shown in FIG. 2E. Similarly, for some embodiments an orientation of each outer frame tissue anchor 54 with respect to upstream support portion 40 (e.g., with respect to one or more inner frame tissue anchors 46 thereof) is the same before and after expansion of tubular portion 32.

For some embodiments, increasing the diameter of tubular portion 32 from d1 to d2 causes greater than 1 mm and/or less than 20 mm (e.g., 1-20 mm, such as 1-10 mm or 5-20 mm) of longitudinal movement of ventricular anchoring support 54 away from coupling point 52. For some embodiments, increasing the diameter of tubular portion 32 from d1 to d2 causes greater than 1 mm and/or less than 20 mm (e.g., 1-20 mm, such as 1-10 mm or 5-20 mm) of longitudinal movement of upstream support portion 40 toward coupling point 52. For some embodiments, distance d3 is 7-30 mm. For some embodiments, distance d4 is 0-15 mm (e.g., 2-15 mm). For some embodiments, increasing the diameter of tubular portion 32 from d1 to d2 reduces the distance between the upstream support portion and ventricular anchoring supports 54 by more than 5 mm and/or less than 30 mm, such as 5-30 mm (e.g., 10-30 mm, such as 10-20 mm or 20-30 mm). For some embodiments, the difference between d3 and d4 is generally equal to the difference between d1 and d2. For some embodiments, the difference between d3 and d4 is more than 1.2 and/or less than 3 times (e.g., 1.5-2.5 times, such as about 2 times) greater than the difference between d1 and d2.

For some embodiments, outer frame tissue anchors 54 curve such that a tip of each ventricular anchoring support 54 is disposed at a shallower angle with respect to inner region 42 of upstream support portion 40, than are portions of ventricular anchor support 50 that are closer to ventricular end 26 of frame assembly 22. For some such embodiments, a tip of each outer frame tissue anchor may be generally parallel with inner region 42. For some such embodiments, while tubular portion 32 is in its expanded state, a tip portion 55 of each outer frame tissue anchor 54 that extends from the tip of the ventricular anchoring support at least 2 mm along the outer frame tissue anchor, is disposed within 2 mm of upstream support portion 40. Thus, for some embodiments, while tubular portion 32 is in its expanded state, for at least 5 percent (e.g., 5-8 percent, or at least 8 percent) of span 18 of upstream support portion 40, the upstream support portion is disposed within 2 mm of a ventricular anchoring support 54.

For some embodiments, in the absence of any obstruction (such as tissue of the valve or covering 23) between ventricular anchoring support 54 and upstream support portion 40, increasing the diameter of tubular portion 32 from d1 to d2 causes the outer frame tissue anchor 54 and the upstream support portion to move past each other (e.g., the outer frame tissue anchor 54 may move between inner frame tissue anchors 46 of the upstream support portion), such that the outer frame tissue anchor 54 is closer to the atrial end of prosthetic valve 20 than is the upstream support portion, e.g., as shown hereinbelow for frame assemblies 122 and 222, mutatis mutandis. (For embodiments in which upstream support portion 40 is covered by covering 23, ventricular anchoring supports 54 typically don't pass the covering. For example, in the absence of any obstruction, ventricular anchoring supports 54 may pass between inner frame tissue anchors 46, and press directly against covering 23.) It is hypothesized that for some embodiments this configuration applies greater force to the valve tissue being sandwiched, and thereby further facilitates anchoring of the implant. That is, for some embodiments, distance d3 is smaller than the sum of distance d5 and a distance d14 (described with reference to FIG. 3C). For some embodiments, increasing the diameter of tubular portion 32 from d1 to d2 advantageously causes ventricular anchoring supports 54 and upstream support portion 40 to move greater than 3 mm and/or less than 25 mm (e.g., greater than 5 mm and/or less than 15 mm, e.g., 5-10 mm, such as about 7 mm) with respect to each other (e.g., toward each other and then past each other).

In some embodiments, in the expanded state of frame assembly 22, upstream support portion 40 has an inner region (e.g., an inner ring) 42 that extends radially outward at a first angle with respect to axis ax1 (and typically with respect to tubular portion 32), and an outer region (e.g., an outer ring) 44 that extends, from the inner region, further radially outward from the tubular portion at a second angle with respect to the tubular portion, the second angle being smaller than the first angle. For example, for some embodiments inner region 42 extends radially outward at an angle alpha_1 of 60-120 degrees (e.g., 70-110 degrees) with respect to axis ax1, and outer region 44 extends radially outward at an angle alpha_2 of 5-70 degrees (e.g., 10-60 degrees) with respect to axis ax1.

It is to be noted that angles alpha_1 and alpha_2 are measured between the respective region support portion 40, and the portion of axis ax1 that extends in an upstream direction from the level of frame assembly 22 at which the respective region begins to extend radially outward.

For some embodiments in which prosthetic valve 20 is configured to be placed at an atrioventricular valve (e.g., a mitral valve or a tricuspid valve) of the subject, region 42 is configured to be placed against the upstream surface of the annulus of the atrioventricular valve, and region 44 is configured to be placed against the walls of the atrium upstream of the valve.

For some embodiments, outer region 44 is more flexible than inner region 42. For example, and as shown, each inner frame tissue anchor 46 may have a different structure in region 44 than in region 42. It is hypothesized that the relative rigidity of region 42 provides resistance against ventricular migration of prosthetic valve 20, while the relative flexibility of region 44 facilitates conformation of upstream support portion 40 to the atrial anatomy.

For some embodiments, two or more of inner frame tissue anchors 46 are connected by a connector (not shown), reducing the flexibility, and/or the independence of movement of the connected inner frame tissue anchors relative to each other. For some embodiments, inner frame tissue anchors 46 are connected in particular sectors of upstream support portion 40, thereby making these sectors more rigid than sectors in which the inner frame tissue anchors are not connected. For example, a relatively rigid sector may be provided to be placed against the posterior portion of the mitral annulus, and a relatively flexible sector may be provided to be placed against the anterior side of the mitral annulus, so as to reduce forces applied by upstream support portion 40 on the aortic sinus.

For some embodiments, and as shown, coupling points 52 are disposed closer to ventricular end 26 of frame assembly 22 than are outer frame tissue anchors 54, or is upstream support portion 40.

As described in more detail with respect to FIGS. 4A-F, the movement of outer frame tissue anchor 54 away from coupling point 52 (and the typical movement of upstream support portion 40 toward the coupling point) facilitates the sandwiching of tissue of the native valve (e.g., leaflet and/or annulus tissue) between the outer frame tissue anchor 54 and the upstream support portion, thereby securing prosthetic valve 20 at the native valve.

Typically, in the compressed state of tubular portion 32, a ventricular end of each ventricular anchor support 50 is longitudinally closer than valve-frame coupling elements 31 to ventricular end 36, and outer frame tissue anchor 54 of each ventricular anchor support 50 is disposed longitudinally closer than the valve-frame coupling elements to atrial end 34. Typically, this is also the case in the expanded state of tubular portion 32.

FIGS. 3A-C show structural changes in frame assembly 22 during transitioning of the assembly between its compressed and expanded states, in accordance with some embodiments of the invention. FIGS. 3A-C each show a portion of the frame assembly, the structural changes thereof being representative of the structural changes that occur in other portions of the frame assembly. FIG. 3A shows a ventricular anchor support 50 and struts 70 (e.g., a portion of outer frame 60), and illustrates the structural changes that occur around outer frame 60. FIG. 3B shows a portion of inner frame 30, and illustrates the structural changes that occur around the inner frame. FIG. 3C shows inner frame 30 as a whole. In each of FIGS. 3A-C, state (A) illustrates the structure while frame assembly 22 (and in particular tubular portion 32) is in its compressed state, and state (B) illustrates the structure while the frame assembly (and in particular tubular portion 32) is in its expanded state.

FIG. 3A shows structural changes in the coupling of ventricular anchoring supports 50 to coupling point 52 (e.g., structural changes of outer frame 60) during the transitioning of frame assembly 22 (and in particular tubular portion 32) between its compressed and expanded states. Each ventricular anchor support 50 is coupled to inner frame 30 via at least one strut 70, which connects the ventricular anchoring support to coupling point 52. Typically, each ventricular anchor support 50 is coupled to inner frame 30 via a plurality of struts 70. A first end 72 of each strut 70 is coupled to ventricular anchor support 50, and a second end 74 of each strut is coupled to a coupling point 52. As described hereinabove, for embodiments in which frame 60 comprises ring 66, each ventricular anchor support 50 is coupled to the ring at a respective trough 62. Ring 66 may comprise struts 70, extending between the peaks and troughs, with each first end 72 at (or close to) a trough 62, and each second end 74 at (or close to) a peak 64.

In the compressed state of frame assembly 22 (and in particular of tubular portion 32), each strut 70 is disposed at a first angle in which first end 72 is disposed closer than second end 74 to the ventricular end of the frame assembly. Expansion of frame assembly 22 (and in particular of tubular portion 32) toward its expanded state causes strut 70 to deflect to a second angle. This deflection moves first end 72 away from the ventricular end of frame assembly 22. That is, in the expanded state of frame assembly 22, first end 72 is further from the ventricular end of the frame assembly than it is when the frame assembly is in its compressed state. This movement is shown as a distance d5 between the position of end 72 in state (A) and its position in state (B). This movement causes the above-described movement of outer frame tissue anchors 54 away from coupling points 52. As shown, outer frame tissue anchors 54 typically move the same distance d5 in response to expansion of frame assembly 22.

For embodiments in which outer frame 60 comprises ring 66, the pattern of alternating peaks and troughs may be described as having an amplitude longitudinally between the peaks and troughs, i.e., measured parallel with central longitudinal axis ax1 of frame assembly 22, and the transition between the compressed and expanded states may be described as follows: In the compressed state of frame assembly 22 (and in particular of tubular portion 32), the pattern of ring 66 has an amplitude d20. In the expanded state frame assembly 22 (and in particular of tubular portion 32), the pattern of ring 66 has an amplitude d21 that is lower than amplitude d20. Because (i) it is at peaks 64 that ring 66 is coupled to inner frame 30 at coupling points 52, and (ii) it is at troughs 62 that ring 66 is coupled to ventricular anchoring supports 50, this reduction in the amplitude of the pattern of ring 66 moves ventricular anchoring supports 50 (e.g., outer frame tissue anchors 54 thereof) longitudinally further from the ventricular end of the frame assembly. The magnitude of this longitudinal movement (e.g., the difference between magnitudes d20 and d21) is equal to d5.

Typically, distance d5 is the same distance as the distance that outer frame tissue anchor 54 moves away from coupling point 52 during expansion of the frame assembly. That is, a distance between outer frame tissue anchor 54 and the portion of ventricular anchor support 50 that is coupled to strut 70, typically remains constant during expansion of the frame assembly. For some embodiments, the longitudinal movement of outer frame tissue anchor 54 away from coupling point 52 is a translational movement (e.g., a movement that does not include rotation or deflection of the outer frame tissue anchor 54).

For some embodiments, a distance d6, measured parallel to axis ax1 of frame assembly 22, between coupling point 52 and first end 72 of strut 70 while assembly 22 is in its compressed state, is 3-15 mm. For some embodiments, a distance d7, measured parallel to axis ax1, between coupling point 52 and first end 72 of strut 70 while assembly 22 is in its expanded state, is 1-5 mm (e.g., 1-4 mm).

For some embodiments, amplitude d20 is 2-10 mm (e.g., 4-7 mm). For some embodiments, amplitude d21 is 4-9 mm (e.g., 5-7 mm).

For some embodiments, and as shown, in the expanded state, first end 72 of strut 70 is disposed closer to the ventricular end of frame assembly 22 than is coupling point 52. For some embodiments, in the expanded state, first end 72 of strut 70 is disposed further from the ventricular end of frame assembly 22 than is coupling point 52.

For embodiments in which frame assembly 22 comprises a plurality of ventricular anchoring supports 50 and a plurality of coupling points 52 (e.g., for embodiments in which the frame assembly comprises outer frame 60) expansion of the frame assembly increases a circumferential distance between adjacent coupling points 52, and an increase in a circumferential distance between adjacent ventricular anchoring supports 50. FIG. 3A shows such an increase in the circumferential distance between adjacent coupling points 52, from a circumferential distance d8 in the compressed state to a circumferential distance d9 in the expanded state. For some embodiments, distance d8 is 1-6 mm. For some embodiments, distance d9 is 3-15 mm.

For some embodiments, in addition to being coupled via ring 66 (e.g., struts 70 thereof) ventricular anchoring supports 50 are also connected to each other via connectors 78. Connectors 78 allow the described movement of ventricular anchoring supports 50 during expansion of frame assembly 22, but typically stabilize ventricular anchoring supports 50 relative to each other while the frame assembly is in its expanded state. For example, connectors 78 may bend and/or deflect during expansion of the frame assembly.

FIGS. 3B-C show structural changes in inner frame 30 during the transitioning of frame assembly 22 between its compressed and expanded states. Tubular portion 32 of inner frame 30 is defined by a plurality of cells 80, which are defined by the repeating pattern of the inner frame. When frame assembly 22 is expanded from its compressed state toward its expanded state, cells 80 (i) widen from a width d10 to a width d11 (measured orthogonal to axis ax1 of the frame assembly), and (ii) shorten from a height d12 to a height d13 (measured parallel to axis ax1 of the frame assembly). This shortening reduces the overall height (i.e., a longitudinal length between atrial end 34 and ventricular end 36) of tubular portion 32 from a height d22 to a height d23, and thereby causes the above-described longitudinal movement of upstream support portion 40 toward coupling points 52 by a distance d14 (shown in FIG. 3C). For some embodiments, and as shown, coupling points 52 are disposed at the widest part of each cell.

Due to the configurations described herein, the distance by which outer frame tissue anchors 54 move with respect to (e.g., toward, or toward-and-beyond) upstream support portion 40 (e.g., inner frame tissue anchors 46 thereof), is typically greater than the reduction in the overall height of tubular portion 32 (e.g., more than 20 percent greater, such as more than 30 percent greater, such as more than 40 percent greater). That is, prosthetic valve 20 comprises: a inner frame (30) that comprises a tubular portion (32) that circumscribes a longitudinal axis (ax1) of the inner frame so as to define a lumen (38) along the axis, the tubular portion having an atrial end (34), a ventricular end (36), a longitudinal length therebetween, and a diameter (e.g., d1 or d2) transverse to the longitudinal axis; a valve member (58), coupled to the tubular portion, disposed within the lumen, and arranged to provide unidirectional upstream-to-downstream flow of blood through the lumen; an upstream support portion (40), coupled to the tubular portion; and an outer frame (60), coupled to the tubular portion, and comprising a outer frame tissue anchor (54), wherein: the implant has a first state (e.g., as shown in FIG. 2D and FIG. 4D) and a second state (e.g., as shown in FIG. 2E and FIG. 4E), in both the first state and the second state, (i) the upstream support portion extends radially outward from the tubular portion, and (ii) the outer frame tissue anchor 54 extends radially outward from the tubular portion, and the tubular portion, the upstream support portion, and the outer frame are arranged such that transitioning of the implant from the first state toward the second state: increases the diameter of the tubular portion by a diameter-increase amount (e.g., the difference between d1 and d2), decreases the length of the tubular portion by a length-decrease amount (e.g., the difference between d22 and d23), and moves the outer frame tissue anchor 54 a longitudinal distance with respect to (e.g., toward or toward-and-beyond) the upstream support portion (e.g., the difference between d3 and d4), this distance being greater than the length-decrease amount.

As shown in the figures, inner frame 30 is typically coupled to outer frame 60 by coupling between (i) a valve-frame coupling element 31 defined by inner frame 30, and (ii) an outer-frame coupling element 61 defined by outer frame 60 (e.g., an outer-frame coupling element is coupled to end 74 of each strut). Typically, elements 31 and 61 are fixed with respect to each other. Each coupling point 52 is thereby typically defined as the point at which a valve-frame coupling element and a corresponding outer-frame coupling element 61 are coupled (e.g., are fixed with respect to each other). For some embodiments, and as shown, elements 31 and 61 are eyelets configured to be coupled together by a connector, such as a pin or suture. For some embodiments, elements 31 and 61 are soldered or welded together.

Typically, and as shown, valve-frame coupling elements 31 are defined by tubular portion 32, and are disposed circumferentially around central longitudinal axis ax1. Outer-frame coupling elements 61 are coupled to ring 66 (or defined by frame 60, such as by ring 66) at respective peaks 64.

As shown (e.g., in FIGS. 2A-E), inner frame 30 (e.g., tubular portion 32 thereof) and outer frame 60 (e.g., ring 66 thereof) are arranged in a close-fitting coaxial arrangement, in both the expanded and compressed states of frame assembly 22. Ignoring spaces due to the cellular structure of the frames, a radial gap d19 between inner frame 30 (e.g., tubular portion 32 thereof) and outer frame 60 (e.g., ring 66 thereof) is typically less than 2 mm (e.g., less than 1 mm), in both the compressed and expanded states, and during the transition therebetween. This is facilitated by the coupling between frames 30 and 60, and the behavior, described hereinabove, of frame 60 in response to changes in the diameter of tubular portion 32 (e.g., rather than solely due to delivery techniques and/or tools). For some embodiments, more than 50 percent (e.g., more than 60 percent) of ring 66 is disposed within 2 mm of tubular portion 32 in both the compressed and expanded states, and during the transition therebetween. For some embodiments, more than 50 percent (e.g., more than 60 percent) of outer frame 60, except for outer frame tissue anchors 54, is disposed within 2 mm of tubular portion 32 in both the compressed and expanded states, and during the transition therebetween.

The structural changes to frame assembly 22 (e.g., to outer frame 60 thereof) are described hereinabove as they occur during (e.g., as a result of) expansion of the frame assembly (in particular tubular portion 32 thereof). This is the natural way to describe these changes because, as described hereinbelow with respect to FIGS. 4A-6 , assembly 22 is in its compressed state during percutaneous delivery to the implant site, and is subsequently expanded. However, the nature of prosthetic valve 20 may be further understood by describing structural changes that occur during compression of the frame assembly (e.g., a transition from the expanded state in FIG. 2E to the intermediate state in FIG. 2D), in particular tubular portion 32 thereof (including if tubular portion 32 were compressed by application of compressive force to the tubular portion, and not to frame 60 except via the tubular portion pulling frame 60 radially inward). Such descriptions may also be relevant because prosthetic valve 20 is typically compressed (i.e., “crimped”) soon before its percutaneous delivery, and therefore these changes may occur while prosthetic valve 20 is in the care of the operating physician.

For some embodiments, the fixation of peaks 64 to respective sites of tubular portion 32 is such that compression of the tubular portion from its expanded state toward its compressed state such that the respective sites of the tubular portion pull the peaks radially inward via radially-inward tension on coupling points 52: (i) reduces a circumferential distance between each of the coupling points and its adjacent coupling points (e.g., from d9 to d8), and (ii) increases the amplitude of the pattern of ring 66 (e.g., from d21 to d20).

For some embodiments, the fixation of outer-frame coupling elements 61 to valve-frame coupling elements 31 is such that compression of tubular portion 32 from its expanded state toward its compressed state such that the valve-frame coupling elements pull the outer-frame coupling elements radially inward: (i) reduces a circumferential distance between each of the outer-frame coupling elements and its adjacent outer-frame coupling elements (e.g., from d9 to d8), and (ii) increases the amplitude of the pattern of ring 66 (e.g., from d21 to d20).

For some embodiments, the fixation of peaks 64 to the respective sites of tubular portion 32 is such that compression of the tubular portion from its expanded state toward its compressed state (i) pulls the peaks radially inward via radially-inward pulling of the respective sites of the tubular portion on the peaks, (ii) reduces a circumferential distance between each of coupling points 52 and its adjacent coupling points (e.g., from d9 to d8), and (iii) increases the amplitude of the pattern of ring 66 (e.g., from d21 to d20), without increasing radial gap d19 between inner frame 30 (e.g., tubular portion 32 thereof) and the ring by more than 1.5 mm.

For some embodiments, the fixation of outer-frame coupling elements 61 with respect to valve-frame coupling elements 31 is such that compression of tubular portion 32 from its expanded state toward its compressed state (i) pulls outer-frame coupling elements 61 radially inward via radially-inward pulling of valve-frame coupling elements 31 on outer-frame coupling elements 61, (ii) reduces a circumferential distance between each of the outer-frame coupling elements and its adjacent outer-frame coupling elements (e.g., from d9 to d8), and (iii) increases the amplitude of the pattern of ring 66 (e.g., from d21 to d20), without increasing radial gap d19 between inner frame 30 (e.g., tubular portion 32 thereof) and the ring by more than 1.5 mm.

Reference is made to FIGS. 4A-F, which are schematic illustrations of implantation of prosthetic valve 20 at a native valve 10 of a heart 4 of a subject, in accordance with some embodiments of the invention. Valve 10 is shown as a mitral valve of the subject, disposed between a left atrium 6 and a left ventricle 8 of the subject. However prosthetic valve 20 may be implanted at another heart valve of the subject, mutatis mutandis. Similarly, although FIGS. 4A-F show prosthetic valve 20 being delivered transseptally via a sheath 88, the implant may alternatively be delivered by any other suitable route, such as transatrially, or transapically.

Prosthetic valve 20 is delivered, in its compressed state, to native valve 10 using a delivery tool 89 that is operable from outside the subject (FIG. 4A). Typically, prosthetic valve 20 is delivered within a delivery capsule 90 of tool 89, which retains the implant in its compressed state. A transseptal approach, such as a transfemoral approach, is shown. Typically, prosthetic valve 20 is positioned such that at least outer frame tissue anchors 54 are disposed downstream of the native valve (i.e., within ventricle 8). At this stage, frame assembly 22 of prosthetic valve 20 is as shown in FIG. 2A.

Subsequently, outer frame tissue anchors 54 are allowed to protrude radially outward, as described hereinabove, e.g., by releasing them from capsule 90 (FIG. 4B). For example, and as shown, capsule 90 may comprise a distal capsule-portion 92 and a proximal capsule-portion 94, and the distal capsule-portion may be moved distally with respect to prosthetic valve 20, so as to expose outer frame tissue anchors 54. At this stage, frame assembly 22 of prosthetic valve 20 is as shown in FIG. 2B.

Subsequently, prosthetic valve 20 is moved upstream, such that upstream support portion 40, in its compressed state, is disposed upstream of leaflets 12 (i.e., within atrium 6). For some embodiments, the upstream movement of prosthetic valve 20 causes outer frame tissue anchors 54 to engage leaflets 12. However, because of the relatively large distance d3 provided by prosthetic valve 20 (described hereinabove), for some embodiments it is not necessary to move the implant so far upstream that outer frame tissue anchors 54 tightly engage leaflets 12 and/or pull the leaflets upstream of the valve annulus. Upstream support portion 40 is then allowed to expand such that it protrudes radially outward, as described hereinabove, e.g., by releasing it from capsule 90 (FIG. 4D). For example, and as shown, proximal capsule-portion 94 may be moved proximally with respect to prosthetic valve 20, so as to expose upstream support portion 40. At this stage, frame assembly 22 of prosthetic valve 20 is as shown in FIG. 2D, in which: (i) distance d3 exists between upstream support portion 40 and outer frame tissue anchors 54, (ii) the outer frame tissue anchors have span d15, (iii) the upstream support portion has span d17, and (iv) tubular portion 32 has diameter d1.

Typically, expansion of frame assembly 22 is inhibited by distal capsule-portion 92 (e.g., by inhibiting expansion of tubular portion 32), and/or by another portion of delivery tool 89 (e.g., a portion of the delivery tool that is disposed within lumen 38).

Subsequently, prosthetic valve 20 is allowed to expand toward its expanded state, such that tubular portion 32 widens to diameter d2, and the distance between upstream support portion 40 and outer frame tissue anchors 54 reduces to distance d4 (FIG. 4E). This sandwiches tissue of valve 10 (typically including annular tissue and/or leaflets 12) between upstream support portion 40 and outer frame tissue anchors 54, thereby securing prosthetic valve 20 at the valve. FIG. 4F shows delivery capsule 90 having been removed from the body of the subject, leaving prosthetic valve 20 in place at valve 10.

As described hereinabove, prosthetic valve 20 is configured such that when tubular portion 32 is expanded, outer frame tissue anchors 54 and upstream support portion 40 move a relatively large distance toward each other. This enables distance d3 to be relatively large, while distance d4 is sufficiently small to provide effective anchoring. As also described hereinabove, prosthetic valve 20 is configured such that outer frame tissue anchors 54 and upstream support portion 40 can extend radially outward a relatively large distance while tubular portion 32 remains compressed. It is hypothesized that for some embodiments, these configurations (independently and/or together) facilitate effective anchoring of prosthetic valve 20, by facilitating placement of a relatively large proportion of valve tissue (e.g., leaflets 12) between the outer frame tissue anchors 54 and the upstream support portion prior to expanding tubular portion 32 and sandwiching the valve tissue.

It is further hypothesized that the relatively great radially-outward extension of outer frame tissue anchors 54 and upstream support portion 40 prior to expansion of tubular portion 32, further facilitates the anchoring/sandwiching step by reducing radially-outward pushing of the valve tissue (e.g., leaflets 12) during the expansion of the tubular portion, and thereby increasing the amount of valve tissue that is sandwiched.

It is yet further hypothesized that this configuration of prosthetic valve 20 facilitates identifying correct positioning of the implant (i.e., with upstream support portion 40 upstream of leaflets 12 and outer frame tissue anchors 54 downstream of the leaflets) prior to expanding tubular portion 32 and sandwiching the valve tissue.

As shown in FIG. 1A, for some embodiments, in the expanded state of frame assembly 22, prosthetic valve 20 defines a toroidal space 49 between outer frame tissue anchors 54 and upstream support portion 40 (e.g., a space that is wider than distance d4). For example, space 49 may have a generally triangular cross-section. It is hypothesized that for some such embodiments, in addition to sandwiching tissue of the native valve between upstream support portion 40 and outer frame tissue anchors 54 (e.g., the tips of the outer frame tissue anchors), space 49 advantageously promotes tissue growth therewithin (e.g., between leaflet tissue and covering 23), which over time further secures prosthetic valve 20 within the native valve.

Reference is now made to FIG. 5 , which is a schematic illustration of a step in the implantation of prosthetic valve 20, in accordance with some embodiments of the invention. Whereas FIGS. 4A-F show an implantation technique in which outer frame tissue anchors 54 are expanded prior to upstream support portion 40, for some embodiments the upstream support portion is expanded prior to the outer frame tissue anchors 54. FIG. 5 shows a step in such an embodiment.

Reference is again made to FIGS. 2A-5 . As noted hereinabove, prosthetic valve 20 may be implanted by causing outer frame tissue anchors 54 to radially protrude before causing upstream support portion 40 to radially protrude, or may be implanted by causing the upstream support portion to protrude before causing the outer frame tissue anchors 54 to protrude. For some embodiments, prosthetic valve 20 is thereby configured to be deliverable in a downstream direction (e.g., transseptally, as shown, or transapically) or in an upstream direction (e.g., transapically or via the aortic valve). Thus, for some embodiments, an operating physician may decide which delivery route is preferable for a given application (e.g., for a given subject, and/or based on available equipment and/or expertise), and prosthetic valve 20 is responsively prepared for the chosen delivery route (e.g., by loading the implant into an appropriate delivery tool).

It is to be noted that for some embodiments, downstream delivery of prosthetic valve 20 may be performed by expanding outer frame tissue anchors 54 first (e.g., as shown in FIGS. 4A-F) or by expanding upstream support portion 40 first (e.g., as shown in FIG. 5 ). Similarly, for some embodiments upstream delivery of prosthetic valve 20 may be performed by upstream support portion 40 first, or by expanding outer frame tissue anchors 54 first.

Reference is now made to FIG. 6 , which is a schematic illustration of prosthetic valve 20, in the state and position shown in FIG. 4D, in accordance with some embodiments of the invention. For some embodiments, while prosthetic valve 20 is in the state and position shown in FIG. 4D, leaflets 12 of valve 10 are able to move, at least in part in response to beating of the heart. Frame (A) shows leaflets 12 during ventricular systole, and frame (B) shows the leaflets during ventricular diastole. For some such embodiments, blood is thereby able to flow from atrium 6 to ventricle 8, between leaflets 12 and prosthetic valve 20. It is hypothesized that this advantageously facilitates a more relaxed implantation procedure, e.g., facilitating retaining of prosthetic valve 20 in this state and position for a duration of greater than 8 minutes. During this time, imaging techniques may be used to verify the position of prosthetic valve 20, and/or positioning of leaflets 12 between upstream support portion 40 and outer frame tissue anchors 54.

Reference is made to FIGS. 7A-B and 8A-B, which are schematic illustrations of frame assemblies 122 and 222 of respective implants, in accordance with some embodiments of the invention. Except where noted otherwise, frame assemblies 122 and 222 are typically identical to frame assembly 22, mutatis mutandis. Elements of frame assemblies 122 and 222 share the name of corresponding elements of frame assembly 22. Additionally, except where noted otherwise, the implants to which frame assemblies 122 and 222 belong are similar to prosthetic valve 20, mutatis mutandis.

Frame assembly 122 comprises (i) an inner frame 130 that comprises a tubular portion 132 and an upstream support portion 140 that typically comprises a plurality of inner frame tissue anchors 146, and (ii) an outer frame 160 that circumscribes the inner frame, and comprises a plurality of ventricular anchoring supports 150 that each comprise a outer frame tissue anchor 154. As illustrated in FIG. 7B, inner frame tissue anchors 146 may be configured to extend radially outward from inner frame 130 to respective anchor terminal ends 147, and outer frame tissue anchors 154 may be configured to extend radially outward from outer frame 160 to respective anchor terminal ends 155. In some embodiments, and as illustrated in FIG. 7B, inner frame tissue anchors 146 may be configured to extend radially outward beyond terminal ends 155 of the outer frame tissue anchors. In some embodiments, outer frame 160 comprises a ring 166 to which ventricular anchoring supports 150 are coupled. Ring 166 is defined by a pattern of alternating peaks and troughs, the peaks being fixed to frame 130 at respective coupling points 152, e.g., as described hereinabove for frame assembly 22, mutatis mutandis. As illustrated in FIG. 7B, outer frame 160 may be formed at least partially of struts 167, which may intersect at outer frame junctions 169. At some outer frame junctions (e.g. junction 169 in FIG. 7B), an outer frame tissue anchor 154 may intersect with one or more struts 167. As a result, and as illustrated in FIG. 7B, outer frame tissue anchors 154 may extend from a portion of the outer frame 160 separate from the atrial end 163 and from the ventricular end 165 of the outer frame (that is, from junction 169). Thus, rather than extending from a junction 169 a along the atrial end of the outer frame 130, outer frame tissue anchors 154 may extend from a junction 169 in an intermediate portion of the outer frame between atrial end 163 and ventricular end 165. Additionally or alternatively, and as also illustrated in FIG. 7B, inner frame 130 may be formed at least partially of struts 133, which may intersect at inner frame junctions 137. At some inner frame junctions (e.g. junction 137 in FIG. 7B), an inner frame tissue anchor 146 may intersect with one or more struts 133. As a result, and as illustrated in FIG. 7B, inner frame tissue anchors 146 may extend from a portion of the inner frame 130 separate from the ventricular end 136 of the inner frame (that is, from junction 137). As illustrated in the embodiment of FIGS. 7A-7B, inner frame 130 may have a greater axial length than outer frame 160. For example, the ventricular end 136 of the inner frame and the ventricular end 165 of the outer frame may be substantially even (that is, substantially aligned in a common lateral plane extending along the bottom of frame assembly 122 in FIG. 7B), while the atrial end 134 of the inner frame may extend beyond the atrial end 163 of the outer frame. As a result, and as illustrated in FIG. 7B, atrial end 134 of the inner frame may include no connections to outer frame 160, as no portion of outer frame 160 is situated adjacent to atrial end 134 for connection thereto. Inner frame 130 and outer frame 160 may instead be connected at at least one different portion of inner frame 130.

Frame assembly 222 comprises (i) a inner frame 230 that comprises a tubular portion 232 and an upstream support portion 240 that typically comprises a plurality of inner frame tissue anchors 246, and (ii) an outer frame 260 that circumscribes the inner frame, and comprises a plurality of ventricular anchoring supports 250 that each comprise a outer frame tissue anchor 254. As illustrated in FIG. 8B, inner frame tissue anchors 246 may be configured to extend radially outward from inner frame 230 to respective anchor terminal ends 247, and outer frame tissue anchors 254 may be configured to extend radially outward from outer frame 260 to respective anchor terminal ends 255. In some embodiments, and as illustrated in FIG. 8B, inner frame tissue anchors 246 may be configured to extend radially outward beyond terminal ends 255 of the outer frame tissue anchors. In some embodiments, outer frame 260 comprises a ring 266 to which ventricular anchoring supports 250 are coupled. Ring 266 is defined by a pattern of alternating peaks and troughs, the peaks being fixed to frame 230 at respective coupling points 252, e.g., as described hereinabove for frame assembly 22, mutatis mutandis. As illustrated in FIG. 8B, outer frame 260 may be formed at least partially of struts 267, which may intersect at outer frame junctions 269. At some outer frame junctions (e.g. junction 269 in FIG. 8B), an outer frame tissue anchor 254 may intersect with one or more struts 267. Additionally or alternatively, and as also illustrated in FIG. 8B, inner frame 230 may be formed at least partially of struts 233, which may intersect at inner frame junctions 237. At some inner frame junctions (e.g. junction 237 in FIG. 8B), an inner frame tissue anchor 246 may intersect with one or more struts 233.

Whereas inner frame tissue anchors 46 of frame assembly 22 are shown as extending from atrial end 34 of tubular portion 32, inner frame tissue anchors 146 and 246 of frame assemblies 122 and 222, respectively, may extend from sites downstream of atrial end 134, 234 of the inner frame. (This difference may also be made to frame assembly 22, mutatis mutandis.) Similarly, outer frame tissue anchors 154, 254, respectively, may extend from sites downstream of atrial end 163, 263 of the outer frame. Tubular portions 32, 132 and 232 are each defined by a repeating pattern of cells that extends around the central longitudinal axis. Specifically, inner frame 130, 230 may include closed cells 181, 281, which may be formed by the intersection of inner frame struts 133, 233 at inner frame junctions 137, 237. Similarly, outer frame 160, 260 may include closed cells 182, 282, which may be formed by the intersection of outer frame struts 167, 267 at outer frame junctions 169, 269. In some embodiments, and as illustrated in FIGS. 7B and 8B, inner frame cells 181, 281 may have a different shape than outer frame cells 182, 282. For example, as illustrated in FIG. 7B, inner frame cell 181 may have a diamond shape while outer frame cell 182 may have a chevron shape. Typically, and as shown, tubular portions 32, 132 and 232 are each defined by two stacked, tessellating rows of cells. In the expanded state of each tubular portion, these cells are typically narrower at their upstream and downstream extremities than midway between these extremities. For example, and as shown, the cells may be roughly diamond or astroid in shape. In frame assembly 22, each inner frame tissue anchor 46 is attached to and extends from a site 35 that is at the upstream extremity of cells of the upstream row. In contrast, in frame assemblies 122 and 222, each inner frame tissue anchor 146 or 246 is attached to and extends from a site 135 (assembly 122) or 235 (assembly 222) that is at the connection between two adjacent cells of the upstream row (alternatively described as being at the upstream extremity of cells of the downstream row).

It is hypothesized by the inventors that this lower position of the inner frame tissue anchors, while maintaining the length of the lumen of the tubular portion, advantageously reduces the distance that the tubular portion (i.e., the ventricular end thereof) extends into the ventricle of the subject, and thereby reduces a likelihood of inhibiting blood flow out of the ventricle through the left ventricular outflow tract. It is further hypothesized that this position of the inner frame tissue anchors reduces radial compression of the tubular portion by movement of the heart, due to greater rigidity of the tubular portion at sites 135 and 235 (which is supported by two adjacent cells) than at site 35 (which is supported by only one cell).

As shown, in the expanded state of frame assemblies 22, 122 and 222, the ventricular anchoring supports (50, 150 and 250, respectively) are circumferentially staggered with the inner frame tissue anchors of the upstream support portion (46, 146 and 246, respectively). This allows the ventricular anchoring supports to move in an upstream direction between the inner frame tissue anchors during expansion of the tubular portion (32, 132 and 232, respectively), facilitating application of greater sandwiching force on tissue of the native valve. In some embodiments, and as illustrated in FIGS. 7B and 8B, outer frame junctions 171, 271 along the ventricular end 165, 265 of the outer frame may be angularly offset from inner frame junctions 139, 239 along the ventricular end 136, 236 of the inner frame. As a result, outer frame junctions 171, 271 may alternate at a regular interval with inner frame junctions 139, 239 about a circumference of frame assembly 122, 222. As a result of this regular spacing and as illustrated in FIGS. 7B and 8B, an outer frame junction 171, 271 may be equidistant from two consecutive inner frame junctions 139, 239 adjacent to the outer frame junction 171, 271. Similarly, an inner frame junction 139, 239 may be equidistant from two consecutive outer frame junctions 171, 271 adjacent to the inner frame junction 139, 239. Additionally or alternatively, and as illustrated in FIGS. 7B and 8B, the ventricular end 165, 265 of the outer frame may include no connections to inner frame 130, 230, as no portion of inner frame 130, 230 is situated adjacent to ventricular end 165, 265 for connection thereto. Inner frame 130, 230 and outer frame 160, 260 may instead be connected at at least one other portion of outer frame 160, 260. The lower position of the inner frame tissue anchors of assemblies 122 and 222 includes circumferentially shifting the position of the inner frame tissue anchors by the width of half a cell. In order to maintain the circumferential staggering of the inner frame tissue anchors 46, 146, 246 and outer frame tissue anchors 54, 154, 254, rings 166 and 266 (and thereby ventricular anchoring supports 150 and 250) are circumferentially shifted correspondingly. As a result, whereas the peaks of ring 66 generally align with connections between adjacent cells of the downstream row of cells of tubular portion 32 (and are fixed to these sites), the peaks of rings 166 and 266 are generally aligned midway between these sites (i.e., at spaces of the cellular structure of the tubular portion). An appendages 168 (for assembly 122) or 268 (for assembly 222) facilitate fixing of the peak with respect to the tubular structure. In some embodiments, and as illustrated in FIG. 7B, inner frame tissue anchors 146 may be angularly aligned with the inner frame junctions 139 along the ventricular end 136 of the inner frame. Additionally or alternatively, and as also illustrated in FIG. 7B, outer frame tissue anchors 154 may be angularly aligned with junctions 137 a along the atrial end 134 of the inner frame and may be angularly offset from junctions 139 along the ventricular end 136 of the inner frame. In some embodiments, and as illustrated in FIG. 7B, junctions 137 a along the atrial end of the inner frame 130 may be angularly offset from junctions 169 a along the atrial end of the outer frame 160.

For assembly 122, appendages 168 are defined by inner frame 130 (e.g., by tubular portion 132 thereof) and extend (in a downstream direction) to the peaks of ring 166, to which they are fixed. For example, each appendage 168 may define a valve-frame coupling element 131 that is fixed to a respective outer-frame coupling element 161 defined by outer frame 260. Typically, appendages 168 extend from sites 135. Typically, appendages 168 are integral with tubular portion 132 and/or in-plane with the tubular portion (e.g., are part of its tubular shape).

For assembly 222, appendages 268 are defined by outer frame 260, and extend (e.g., in an upstream direction) from the peaks of ring 266. Typically, appendages 268 extend to sites 235, to which they are fixed. For example, each appendage 268 may define an outer-frame coupling element 261 that is fixed to a respective valve-frame coupling element 231 defined by inner frame 230 (e.g., by tubular portion 232 thereof). Typically, appendages 268 are integral with outer frame 260 and/or in-plane with adjacent portions of outer frame 260, such as ring 266.

Therefore, frame assembly 122 defines a hub at site 135, and frame assembly 222 defines a hub at site 235. For some embodiments, apparatus therefore comprises: a plurality of prosthetic valve leaflets; and a frame assembly, comprising: a tubular portion (132 or 232) defined by a repeating pattern of cells, the tubular portion extending circumferentially around longitudinal axis ax1 so as to define a longitudinal lumen, the prosthetic valve leaflets coupled to the inner frame and disposed within the lumen; an outer frame (160 or 260), comprising a plurality of ventricular anchoring supports (150 or 250), distributed circumferentially around the tubular portion, each support having a outer frame tissue anchor (154 or 254); an upstream support portion (140 or 240) that comprises a plurality of inner frame tissue anchors (146 or 246) that extend radially outward from the tubular portion; and a plurality of appendages (168 or 268), each having a first end that defines a coupling element (161 or 261) via which the tubular portion is coupled to the outer frame, and a second end; wherein the frame assembly defines a plurality of hubs (135 or 235), distributed circumferentially around the longitudinal axis on a plane that is transverse to longitudinal axis ax1, each hub defined by convergence and connection of, (i) two adjacent cells of the tubular portion, (ii) an inner frame tissue anchor of the plurality of inner frame tissue anchors, and (iii) an appendage of the plurality of appendages.

Reference is made to FIGS. 9A-C, which are schematic illustrations of a prosthetic valve 320 comprising a frame assembly 322, in accordance with some embodiments of the invention. Except where noted otherwise, frame assembly 322 is identical to frame assembly 122, and prosthetic valve 300 is identical to the prosthetic valve to which frame assembly 122 belongs, mutatis mutandis. FIG. 9A is a side-view of prosthetic valve 320, and FIG. 9B is an isometric bottom-view of the prosthetic valve.

Frame assembly 122 comprises (i) a inner frame 330 that comprises a tubular portion 332 and an upstream support portion 340 that typically comprises a plurality of inner frame tissue anchors 346, and (ii) an outer frame 360 that circumscribes the inner frame, and comprises a plurality of ventricular anchoring supports 350 that each comprise a outer frame tissue anchor 354. Typically, outer frame 360 comprises a ring 366 to which ventricular anchoring supports 350 are coupled. Ring 366 is defined by a pattern of alternating peaks and troughs, the peaks being fixed to frame 330 at respective coupling points 352, e.g., as described hereinabove for frame assembly 22 and/or frame assembly 122, mutatis mutandis.

Frame assembly 322 comprises an annular upstream support portion 340 that has an inner portion 342 that extends radially outward from the upstream portion (e.g., the atrial end) of tubular portion 332. Upstream support portion 340 further comprises one or more fabric pockets 344 disposed circumferentially around inner portion 342, each pocket of the one or more pockets having an opening that faces a downstream direction (i.e., generally toward the ventricular end of prosthetic valve 320). In the figures, upstream support portion 340 has a single toroidal pocket 344 that extends circumferentially around inner portion 342.

Typically, a covering 323 (e.g., similar to covering 23, described hereinabove, mutatis mutandis) is disposed over inner frame tissue anchors 346, thereby forming pocket 344. Further typically, inner frame tissue anchors 346 are shaped to form pocket 344 from covering 323. For example, and as shown, inner frame tissue anchors 346 may curve to form a hook-shape.

For some embodiments, portion 340 has a plurality of separate pockets 344, e.g., separated at inner frame tissue anchors 346. For some such embodiments, covering 323 is loosely-fitted (e.g., baggy) between radially-outward parts of inner frame tissue anchors 346, e.g., compared to inner portion 342, in which the covering is more closely-fitted between radially-inward parts of the inner frame tissue anchors.

FIG. 9C shows prosthetic valve 320 implanted at native valve 10. Pocket 344 is typically shaped and arranged to billow in response to perivalvular flow 302 of blood in an upstream direction. If ventricular systole forces blood in ventricle 8 between prosthetic valve 320 and native valve 10, that blood inflates pocket 344 and presses it (e.g., covering 323 and/or the radially-outward part of inner frame tissue anchor 346) against tissue of atrium 6 (e.g., against the atrial wall), thereby increasing sealing responsively. It is hypothesized by the inventors that the shape and orientation of pocket 344 (e.g., the hook-shape of inner frame tissue anchors 346) facilitates this pressing radially-outward in response to the pocket's receipt of upstream-flowing blood.

Pocket(s) 344 may be used in combination with any of the implants described herein, mutatis mutandis.

Reference is again made to FIGS. 1A-9C. It is to be noted that unless specifically stated otherwise, the term “radially outward” (e.g., used to describe upstream support portion 40 and outer frame tissue anchors 54) means portions of the element are disposed progressively further outward from a central point (such as longitudinal axis ax1 or tubular portion 32), but does not necessarily mean disposed at 90 degrees with respect to longitudinal axis ax1. For example, outer frame tissue anchors 54 may extend radially outward at 90 degrees with respect to longitudinal axis ax1, but may alternatively extend radially outward at a shallower angle with respect to the longitudinal axis.

It will be appreciated by persons skilled in the art that the present invention is not limited to what has been particularly shown and described hereinabove. Rather, the scope of the present invention includes both combinations and subcombinations of the various features described hereinabove, as well as variations and modifications thereof that are not in the prior art, which would occur to persons skilled in the art upon reading the foregoing description. 

1.-72. (canceled)
 73. A prosthetic valve for implantation within a native heart valve, the prosthetic valve comprising: an annular outer frame formed at least partially of outer frame struts intersecting at a plurality of outer frame junctions, the annular outer frame having a plurality of downstream junctions along a downstream end of the outer frame; an inner frame situated at least partially within the annular outer frame, the inner frame formed at least partially of inner frame struts intersecting at a plurality of inner frame junctions, the inner frame having a plurality of downstream junctions along a downstream end of the inner frame; and a plurality of tissue anchors extending from the annular outer frame, wherein the downstream junctions of the annular outer frame are spaced apart circumferentially from the downstream junctions of the inner frame, and the annular outer frame includes at least one anchor support strut extending between a downstream junction of the annular outer frame and a point of connection between at least one tissue anchor and the annular outer frame, the at least one anchor support strut being configured for placement parallel to a longitudinal axis of the prosthetic valve.
 74. The prosthetic valve of claim 73, wherein the at least one anchor support strut is configured to be arranged parallel to the longitudinal axis of the prosthetic valve when the prosthetic valve is in a compressed delivery state.
 75. The prosthetic valve of claim 73, wherein the downstream junctions of the annular outer frame are spaced apart circumferentially from and alternate in a circumferential direction with the downstream junctions of the inner frame.
 76. The prosthetic valve of claim 73, wherein along a circumference of the prosthetic valve: the downstream junctions of the annular outer frame are offset at a regular interval from the downstream junctions of the inner frame, and the inner frame junctions along an upstream end of the inner frame are offset at a regular interval from the outer frame junctions along an upstream end of the annular outer frame.
 77. The prosthetic valve of claim 73, wherein the point of connection between the at least one tissue anchor and the annular outer frame is situated upstream from the downstream junctions of the annular outer frame, such that at least a portion of the annular outer frame is configured to be situated downstream from the at least one tissue anchor.
 78. The prosthetic valve of claim 73, wherein the point of connection between the at least one tissue anchor and the annular outer frame is spaced apart from an upstream end of the annular outer frame and from the downstream end of the annular outer frame.
 79. The prosthetic valve of claim 78, wherein the at least one tissue anchor and at least three outer frame struts intersect at the point of connection between the at least one tissue anchor and the annular outer frame.
 80. The prosthetic valve of claim 73, further comprising: a plurality of inner frame tissue anchors extending from the inner frame, wherein a portion of at least one inner frame tissue anchor is configured to form a radially-outermost portion of the prosthetic valve relative to the longitudinal axis of the prosthetic valve when the at least one inner frame tissue anchor engages the native heart valve.
 81. The prosthetic valve of claim 80, wherein beyond locations of connection to the inner frame, the inner frame tissue anchors are devoid of interconnections therebetween.
 82. The prosthetic valve of claim 80, wherein the at least one inner frame tissue anchor is configured to be situated at the same position along a circumference of the prosthetic valve as at least one downstream junction of the inner frame.
 83. The prosthetic valve of claim 80, wherein the tissue anchors of the annular outer frame are configured to engage native ventricular tissue, and the inner frame tissue anchors are configured to engage native atrial tissue.
 84. The prosthetic valve of claim 80, wherein the inner frame tissue anchors are spaced apart circumferentially from the tissue anchors of the annular outer frame.
 85. The prosthetic valve of claim 73, wherein the inner frame struts intersect at the plurality of inner frame junctions to form at least one closed cell and the outer frame struts intersect at the plurality of outer frame junctions to form at least one closed cell, and wherein the inner frame includes a closed cell having a first shape and the annular outer frame includes a closed cell having a second shape different than the first shape.
 86. A prosthetic valve for implantation within a native heart valve, the prosthetic valve comprising: an annular outer frame formed at least partially of outer frame struts intersecting at a plurality of outer frame junctions, the annular outer frame having a plurality of downstream junctions along a downstream end of the annular outer frame; an inner frame situated at least partially within the annular outer frame, the inner frame formed at least partially of inner frame struts intersecting at a plurality of inner frame junctions, the inner frame having a plurality of downstream junctions along a downstream end of the inner frame, wherein the inner frame is configured to have a greater axial length than the annular outer frame and to extend in a downstream direction beyond the downstream end of the annular outer frame, and the downstream junctions of the annular outer frame are spaced apart circumferentially from the downstream junctions of the inner frame; and a plurality of tissue anchors extending from the annular outer frame, wherein the annular outer frame includes at least one anchor support strut extending between a downstream junction of the annular outer frame and a point of connection between at least one tissue anchor and the annular outer frame, the at least one anchor support strut being configured for placement parallel to a longitudinal axis of the prosthetic valve.
 87. The prosthetic valve of claim 86, wherein the at least one anchor support strut is configured to be arranged parallel to the longitudinal axis of the prosthetic valve when the prosthetic valve is in a compressed delivery state.
 88. The prosthetic valve of claim 86, wherein the downstream junctions of the annular outer frame are spaced apart circumferentially from and alternate in a circumferential direction with the downstream junctions of the inner frame.
 89. The prosthetic valve of claim 86, wherein along a circumference of the prosthetic valve: the downstream junctions of the annular outer frame are offset at a regular interval from the downstream junctions of the inner frame, and the inner frame junctions along an upstream end of the inner frame are offset at a regular interval from the outer frame junctions along an upstream end of the annular outer frame.
 90. The prosthetic valve of claim 86, further comprising: a plurality of inner frame tissue anchors extending from the inner frame, wherein a portion of at least one inner frame tissue anchor is configured to form a radially-outermost portion of the prosthetic valve relative to the longitudinal axis of the prosthetic valve when the at least one inner frame tissue anchor engages the native heart valve.
 91. The prosthetic valve of claim 90, wherein the at least one inner frame tissue anchor is configured to be situated at the same position along a circumference of the prosthetic valve as at least one downstream junction of the inner frame.
 92. The prosthetic valve of claim 90, wherein the inner frame tissue anchors are spaced apart circumferentially from the tissue anchors of the annular outer frame, and beyond locations of connection to the inner frame, the inner frame tissue anchors are devoid of interconnections therebetween. 